CA2275762C - Apparatus for improving vision and resolution of retinal images - Google Patents
Apparatus for improving vision and resolution of retinal images Download PDFInfo
- Publication number
- CA2275762C CA2275762C CA002275762A CA2275762A CA2275762C CA 2275762 C CA2275762 C CA 2275762C CA 002275762 A CA002275762 A CA 002275762A CA 2275762 A CA2275762 A CA 2275762A CA 2275762 C CA2275762 C CA 2275762C
- Authority
- CA
- Canada
- Prior art keywords
- point source
- eye
- retina
- source image
- aberrations
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
- 230000004256 retinal image Effects 0.000 title abstract description 8
- 230000004377 improving vision Effects 0.000 title abstract description 4
- 230000004075 alteration Effects 0.000 claims abstract description 117
- 210000001525 retina Anatomy 0.000 claims abstract description 46
- 230000003287 optical effect Effects 0.000 claims abstract description 34
- 238000000034 method Methods 0.000 claims abstract description 30
- 230000002207 retinal effect Effects 0.000 claims abstract description 23
- 238000012937 correction Methods 0.000 claims abstract description 16
- 230000004438 eyesight Effects 0.000 claims abstract description 12
- 238000001356 surgical procedure Methods 0.000 claims abstract description 7
- 210000004087 cornea Anatomy 0.000 claims description 5
- 238000004519 manufacturing process Methods 0.000 claims description 4
- 239000004973 liquid crystal related substance Substances 0.000 claims description 3
- 201000009310 astigmatism Diseases 0.000 abstract description 13
- 238000003384 imaging method Methods 0.000 abstract description 3
- 230000008569 process Effects 0.000 abstract description 3
- 210000001747 pupil Anatomy 0.000 description 21
- 230000003044 adaptive effect Effects 0.000 description 17
- 238000005259 measurement Methods 0.000 description 7
- 238000013459 approach Methods 0.000 description 3
- 238000010586 diagram Methods 0.000 description 3
- 239000011521 glass Substances 0.000 description 3
- 230000001788 irregular Effects 0.000 description 3
- 206010010071 Coma Diseases 0.000 description 2
- 230000008901 benefit Effects 0.000 description 2
- 208000029436 dilated pupil Diseases 0.000 description 2
- 230000006872 improvement Effects 0.000 description 2
- 229910052743 krypton Inorganic materials 0.000 description 2
- DNNSSWSSYDEUBZ-UHFFFAOYSA-N krypton atom Chemical compound [Kr] DNNSSWSSYDEUBZ-UHFFFAOYSA-N 0.000 description 2
- 238000012014 optical coherence tomography Methods 0.000 description 2
- 230000000007 visual effect Effects 0.000 description 2
- 206010020675 Hypermetropia Diseases 0.000 description 1
- 206010073261 Ovarian theca cell tumour Diseases 0.000 description 1
- 230000002301 combined effect Effects 0.000 description 1
- 238000000354 decomposition reaction Methods 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 238000012631 diagnostic technique Methods 0.000 description 1
- 238000006073 displacement reaction Methods 0.000 description 1
- 230000004305 hyperopia Effects 0.000 description 1
- 201000006318 hyperopia Diseases 0.000 description 1
- 230000007246 mechanism Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 208000001491 myopia Diseases 0.000 description 1
- 230000004379 myopia Effects 0.000 description 1
- 230000001575 pathological effect Effects 0.000 description 1
- 230000037361 pathway Effects 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- 230000003595 spectral effect Effects 0.000 description 1
- 230000003068 static effect Effects 0.000 description 1
- 238000012360 testing method Methods 0.000 description 1
- 208000001644 thecoma Diseases 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/103—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining refraction, e.g. refractometers, skiascopes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/14—Arrangements specially adapted for eye photography
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
- A61B3/14—Arrangements specially adapted for eye photography
- A61B3/15—Arrangements specially adapted for eye photography with means for aligning, spacing or blocking spurious reflection ; with means for relaxing
- A61B3/156—Arrangements specially adapted for eye photography with means for aligning, spacing or blocking spurious reflection ; with means for relaxing for blocking
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
- G01J9/00—Measuring optical phase difference; Determining degree of coherence; Measuring optical wavelength
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Physics & Mathematics (AREA)
- Surgery (AREA)
- General Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Biophysics (AREA)
- Animal Behavior & Ethology (AREA)
- Ophthalmology & Optometry (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Spectroscopy & Molecular Physics (AREA)
- General Physics & Mathematics (AREA)
- Eye Examination Apparatus (AREA)
- Prostheses (AREA)
- Eyeglasses (AREA)
Abstract
An apparatus for improving vision and resolution of retinal images comprises a point source produced on the retina (101) of a living eye (100) by a laser beam (102).
The laser beam reflected from the retina is received at a lenslet array of a Hartmann-Shack wavefront sensor (148) such that each of the lenslets forms an aerial image of the retinal point source on a CCD camera (146) located adjacent to the lenslet array. The output signal from the CCD camera is acquired by a computer (150) which processes the signal and produces a correction signal which may be used to control a compensating optical or wavefront compensation device such as a deformable mirror (118). It may also be used to fabricate a contact lens or intraocular lens, or to guide a surgical procedure to correct the aberrations of the eye. Any of these methods could correct aberrations beyond defocus and astigmatism, allowing improved vision and improved imaging of the inside of the eye.
The laser beam reflected from the retina is received at a lenslet array of a Hartmann-Shack wavefront sensor (148) such that each of the lenslets forms an aerial image of the retinal point source on a CCD camera (146) located adjacent to the lenslet array. The output signal from the CCD camera is acquired by a computer (150) which processes the signal and produces a correction signal which may be used to control a compensating optical or wavefront compensation device such as a deformable mirror (118). It may also be used to fabricate a contact lens or intraocular lens, or to guide a surgical procedure to correct the aberrations of the eye. Any of these methods could correct aberrations beyond defocus and astigmatism, allowing improved vision and improved imaging of the inside of the eye.
Description
APPARATUS FOR IMPROVING VISION AND RESOLUTION OF RECINAL IMAGES
BACKGROUND OF THE INVENTION
The present invention is directed to a method of and an apparatus for improving vision and the resolution of retinal images. More particularly, the present invention is directed to a method of and an apparatus for measuring and correcting the wave aberration of the eye such that the measured data can be used to develop corrective optical elements for improving the optical quality of the eye.
Despite significant advances in spectacle and contact lens design, current ophthalmic lenses still can only correct defocus and astigmatism. Spectacles and contact lenses leave uncorrected additional aberrations such as spherical aberration, coma, and a host of irregular aberrations. These high order aberrations of the eye not only blur images formed on the retina, which impairs vision, but also blur images taken of the living human retina. There have been two obstacles that prevent the use of specially-designed optical elements to correct aberrations beyond defocus and astigmatism in the eye. First, quantitative measurement of the irregular aberrations of the eye has not been possible. Second, a mechanism to correct the monochromatic aberrations of the eye other than defocus and astigmatism has not been demonstrated.
Subjective refractive methods of optometrists and objective autorefractors measure defocus and astigmatism only. They cannot measure the complete wave aberration of the eye, which includes all aberrations left uncorrected by conventional spectacles.
The objective aberroscope disclosed by Walsh et al. in the Journal of the Optical Society ofAmerica A, Vol.
1, pp. 987-992 (1984) provides simultaneous wave aberration measurements of the entire pupil but cannot sample the pupil with a spacing finer than about 0.9 mm (See Charman in Optometry and Vision Science, Vol. 68, pp. 574-583 (1991)). Moreover, rapid, automated computation of the wave aberration has not been demonstrated with this method.
Recently, one of the co-inventors herein, together with others, developed an apparatus to measure the wave aberration of the eye. In a report entitled "Objective measurement of wave aberrations of the human eye with the use of a Hartmann-Shack wave-front sensor", Liang et al., J. Opt. Soc. Am. A., volume 11, number 7, pp. 1-9, July 1994, the authors disclosed a Hartmann-Shack wavefront sensor that they used to measure the wave aberrations of the human eye by sensing the wavefront emerging from the eye produced by the retinal reflection of a focused light beam on the fovea. Using the system disclosed therein, the authors were able to measure only up to fourth order polynomial functions. The wavefront :fitting with polynomials up to fourth order does not provide a complete description of the eye's aberrations. That description is generally insufficient to accurately compute the optical perfoirmance of the eye. This instrument was not equipped to remove unwanted light reflected from other surfaces, such as lenses and the cornea of the eye.
There has also been a previous attempt to correct the monochromatic aberrations of the eye beyond defocus and astigmatism, with the goal of improving the axial resolution of the confocal scanning laser ophthalmoscope. Bartsch et al., in Vision Science and its Applications, 1994, Technical Digest Series, Vol. 2 (Optical Society of America, Washington, D.C.) pp. 134- 137 (1994) used a fundus contact lens to null the refraction at the first surface of the cornea. That approach, however, suffers from the fundamental problem that the wave aberration of the eye depends on the combined effects of refractive index variations throughout the eye's optics. Possibly for that reasori, an attempt to use a fundus contact lens to increase the axial resolution of a confocal scanning laser ophthalmoscope showed only modest improvement.
Another approach is to use a deformable miiror, a device that has successfully compensated for atmospheric turbulence in ground-based telescopes. A
deformable mirror was previously proposed for use in a confocal laser scanning ophthalmoscope in conjunction with the human eye in U.S. Pat. No. 4,838,679 to Bille, but no method to measure the wave aberration of the eye was proposed or disclosed. Dreher, Bille, and Weinreb, in Applied Optics, Vol. 28, pp. 804-808 demonstrated the only usage of a deformable mirror for the eye, but only corrected the astigmatism of the eye, which is no better than the correction provided by conventional ophthalmic lenses. The use of an optical element to correct monochromatic aberrations higher than second order has never been achieved. In both those systems, no appropriate method for measuring the eye's high order aberrations was disclosed. Bille et al., in Noninvasive Diagnostic Techniques in Ophthalmology, edited by Masters, B.
R., Springer-Verlag, pp. 528-547 (1990) proposed the use of a wavefront sensor in conjunction with a deformable mirror, but a working system wa.; never disclosed or realized.
BACKGROUND OF THE INVENTION
The present invention is directed to a method of and an apparatus for improving vision and the resolution of retinal images. More particularly, the present invention is directed to a method of and an apparatus for measuring and correcting the wave aberration of the eye such that the measured data can be used to develop corrective optical elements for improving the optical quality of the eye.
Despite significant advances in spectacle and contact lens design, current ophthalmic lenses still can only correct defocus and astigmatism. Spectacles and contact lenses leave uncorrected additional aberrations such as spherical aberration, coma, and a host of irregular aberrations. These high order aberrations of the eye not only blur images formed on the retina, which impairs vision, but also blur images taken of the living human retina. There have been two obstacles that prevent the use of specially-designed optical elements to correct aberrations beyond defocus and astigmatism in the eye. First, quantitative measurement of the irregular aberrations of the eye has not been possible. Second, a mechanism to correct the monochromatic aberrations of the eye other than defocus and astigmatism has not been demonstrated.
Subjective refractive methods of optometrists and objective autorefractors measure defocus and astigmatism only. They cannot measure the complete wave aberration of the eye, which includes all aberrations left uncorrected by conventional spectacles.
The objective aberroscope disclosed by Walsh et al. in the Journal of the Optical Society ofAmerica A, Vol.
1, pp. 987-992 (1984) provides simultaneous wave aberration measurements of the entire pupil but cannot sample the pupil with a spacing finer than about 0.9 mm (See Charman in Optometry and Vision Science, Vol. 68, pp. 574-583 (1991)). Moreover, rapid, automated computation of the wave aberration has not been demonstrated with this method.
Recently, one of the co-inventors herein, together with others, developed an apparatus to measure the wave aberration of the eye. In a report entitled "Objective measurement of wave aberrations of the human eye with the use of a Hartmann-Shack wave-front sensor", Liang et al., J. Opt. Soc. Am. A., volume 11, number 7, pp. 1-9, July 1994, the authors disclosed a Hartmann-Shack wavefront sensor that they used to measure the wave aberrations of the human eye by sensing the wavefront emerging from the eye produced by the retinal reflection of a focused light beam on the fovea. Using the system disclosed therein, the authors were able to measure only up to fourth order polynomial functions. The wavefront :fitting with polynomials up to fourth order does not provide a complete description of the eye's aberrations. That description is generally insufficient to accurately compute the optical perfoirmance of the eye. This instrument was not equipped to remove unwanted light reflected from other surfaces, such as lenses and the cornea of the eye.
There has also been a previous attempt to correct the monochromatic aberrations of the eye beyond defocus and astigmatism, with the goal of improving the axial resolution of the confocal scanning laser ophthalmoscope. Bartsch et al., in Vision Science and its Applications, 1994, Technical Digest Series, Vol. 2 (Optical Society of America, Washington, D.C.) pp. 134- 137 (1994) used a fundus contact lens to null the refraction at the first surface of the cornea. That approach, however, suffers from the fundamental problem that the wave aberration of the eye depends on the combined effects of refractive index variations throughout the eye's optics. Possibly for that reasori, an attempt to use a fundus contact lens to increase the axial resolution of a confocal scanning laser ophthalmoscope showed only modest improvement.
Another approach is to use a deformable miiror, a device that has successfully compensated for atmospheric turbulence in ground-based telescopes. A
deformable mirror was previously proposed for use in a confocal laser scanning ophthalmoscope in conjunction with the human eye in U.S. Pat. No. 4,838,679 to Bille, but no method to measure the wave aberration of the eye was proposed or disclosed. Dreher, Bille, and Weinreb, in Applied Optics, Vol. 28, pp. 804-808 demonstrated the only usage of a deformable mirror for the eye, but only corrected the astigmatism of the eye, which is no better than the correction provided by conventional ophthalmic lenses. The use of an optical element to correct monochromatic aberrations higher than second order has never been achieved. In both those systems, no appropriate method for measuring the eye's high order aberrations was disclosed. Bille et al., in Noninvasive Diagnostic Techniques in Ophthalmology, edited by Masters, B.
R., Springer-Verlag, pp. 528-547 (1990) proposed the use of a wavefront sensor in conjunction with a deformable mirror, but a working system wa.; never disclosed or realized.
SUMMARY AND OBJECTS OF THE INVENTION
In view of the foregoing, it is apparent that there exists a need in the art for a method of and an apparatus for producing ophthalmic optical elements that provide improved or supernormal vision over that which is currently avail[able, as well as high resolution retinal images. It is, therefore, a primary object of the present invention to provide a method of and an apparatus for accurately measuring higher order aberrations of the eye and for using the data thus measured to compensate for those aberrations with a customized optical element.
It is also an object of the present invention to provide an improved wavefront sensor which rejects light reflected from structures other than the retina and which is capable of providing a complete measurement of the eye's aberrations.
It is a further object of the present invention to utilize such an improved wavefront sensor in combination with a deformable mirror to correct the wave aberration in a feedback manner such that the subject achieves normal or supernormal vision.
It is likewise a primary object of the present invention to provide a method of and an apparatus for producing high resolution retinal images which allow the imaging of microscopic structures the size of single cells in a human retina.
Briefly described, these and other objects of the invention are accomplished by providing a system for receiving light reflected from a retina of an eye. The wavefront in the plane of the pupil is recreated in the plane of a lenslet array of a Hartmann-Shack wavefront sensor. Each of the lenslets in the lenslet array is used to form an aerial image of the retinal point source on a CCD camera located adjacent to the lenslet array. The wave aberration of the eye, in the form of a point source produced on the retina by a laser beam, displaces each spot by an amount proportional to the local slope of the wavefront at each of the lenslets. The output from the digital CCD camera is sent to a computer which then calculates the wave aberration and provides a signal to a deformable mirror. Following an iterative procedure, the deformable mirror ultimately acquires a shape that is identical to the wave aberration measured at the outset, but with half the ainplitude. This deformation is the appropriate one to flatten the distorted wavefront into a plane wave, which improves image quality.
In its method aspects, the system of the present invention, using the computer, first acquires the CCD image, as described above. Then, the computer computes the centroid of the spot formed by each of the lenslets of the wavefcont sensor. Shifts in each focus spot in the x and y directions are calculated and then used as the slope data to fit with the sum of the first derivatives of 65 Zernike polynomials, using a least squares procedure, to determine the weight for each polynomial.
Then, the Zemike polynomials are weighted with the calculated coefficients.
The 65 polynomials in the wavefront fit include all Zemike modes with radial power less than or equal to 10, except for the piston term.
The weighted Zemike polynomials are then added together, to result in the reconstructed wave aberration. The wave aberration is then evaluated at the locations of the actuators of a deformable mirror in order to produce the correction signal which is sent by the computer to the wavefront compensation device or deformable mirror, as discussed above.
Such a feedback loop continues to receive the reconstructed wave aberration results, feeding back an appropriate correction signal, until the RMS of the reconstructed wave aberration signal reaches an asymptotic value, at which point, the deformable mirror has been deformed such that it will compensate for all the detected aberrations of the eye.
When the reconstructed wave aberration sigr.ial reaches its asymptotic value, the final aberration signal (including all of the previously genierated signals up until the RMS error reaches the asymptotic value) can be used to produae. contact lenses to correct for all of the monochromatic aberrations of the human eye or for surgical procedures.
The present invention can also be used to provide high resolution images of the retina.
The system for producing such images uses a krypton flash lamp which is designed to illuminate a retinal disk to provide an image of the retina which is reflected by the deformable mirror onto a lens and through an aperture such that the reflected image of the retina is focused onto a second CCD camera. The signals generated by the camera are acquired in a manner similar to that described above in connectiori with the first CCD
camera and are stored for later use in the computer.
With these and other objects, advantages, and features of the invention that may become hereinafter apparent, the nature of the invention may be more clearly understood by reference to the following detailed description of the invention, the appended claims and to the drawings attached herein.
BRIEF DESCRIPTION OF THE DRAWINGS
Fig. 1 is a schematic diagram of the system of the present invention;
Fig. 2 is a diagram of a flow chart of a method for the present invention for use in fabricating contact lenses or providing retinal images using the apparatus shown in Fig. 1;
Figs. 3a-3d show the wave aberration and the corresponding point spread functions before and after adaptive compensation using the system of the present invention, respectively; and, Fig. 4 shows the Zernike decomposition of the wave aberration of the eye before and after adaptive compensation, showing that the invention can correct not only second order aberrations (defocus and astigmatism) but also high=-order aberrations.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT
Referring now to Fig. 1, there is shown, in schematic diagram form, the apparatus of the present invention which can be used to both improve visual performance and to provide high resolution retinal images of eyes. The apparatus of the present invention, as shown in Fig. 1, measures the aberrations of the eye using a Hartmann-Shack wavefront sensor and then corrects them in a closed feedback loop with a compensating optical component such as a deformable mirror.
To measure the eye's wave aberration, a point source is produced on the retina by a laser 102. The light from the laser 102, is controlleci by a shutter (not shown). The laser light passes through a spatial filter 104 and is collimated by an achromatic doublet lens 106. The collimated laser beam is reflected by the polarizing 'beamsplitter 110, passes through the lenses 112 and 116, and is incident onto a deformable mirror 118. The laser beam reflected from the deformable mirror 118 is focused by the lens 120, passes through the lens 122 and the second beamsplitter 124 and reaches the eye 100 at a diameter of about 1.5 mm at the pupil. The lens of the eye 100 focuses the laser beain on its retina 101.
Possible myopia or hyperopia of the tested eye is corrected by movemetit of the eye 100 and the lens 122 with respect to the lens 120.
The light reflected from the retina 101 forms a distorted wavefront at the pupil, which is recreated in the plane of the deformable mirror 118 by the lenses 122 and 120, and also in the plane of the lenslet array of a Hartmann-Shack viiavefront sensor 148 by the lenses 116 and 112. The pupil is conjugate with a two-dimensional array of lenslets 148.
Each of the lenslets in the array 148 forms an aerial image of the retinal point source on the CCD camera 146. The CCD camera 146 sends the digitized image to the computer 150 where it is stored in RAM or on magnetic or other storage media.
Aberrations displace each spot by an amount proportional to the local slope of the wavefront at each lenslet. The slope of the wavefroiit can be determined from the displacement of these spots relative to a known aberration-free reference. The wavefront sensor 154 measures the local slopes in both the x and y directions at 2171ocations simultaneously across the dilated pupil. From the array of slopes, the wave aberration is reconstructed as described later herein.
The beamsplitter 110 which forms part of the wavefront sensor 154 is preferably configured as a polarizing beamsplitter in order to remove unwanted light reflected from the first surface of the comea of the eye 100 and other optical elements, such as lenses 112, 116, 120, and 122. Such light would otherwise interfere with the operation of the wavefront sensor 154 and would make automatic procedures for measuring the wave aberration more difficult.
The wavefront sensor 154 of the present invention provides a much more complete measurement of the aberrations of the eye than has been possible before in part because a large number of samples in the pupil of the eye are used. Using the apparatus of the present invention, it has been found that the eye 100 contains complex abeffations that are not corrected by spectacles or contact lenses, and that such aberrations are significant when the pupil is large. Even aberrations of order 5 and greater, which the present wavefront sensor 154 is the first to measure, has significant impact on the eye's optical quality. Moreover, the higher order aberrations are stable over time. Such stability is important because it shows that the aberrations can be corrected using a static optical corrector, such as a custom-made contact lens.
Once the wave aberration is measured, as described above, it is compensated with a device conjugate with the pupil of the eye 100 that can control the phase of the light at different points in the pupil. As will be further described in detail in connection with Fig. 2, the computer 150, under software control, produces a correction signal which is fed back to the defonmable mirror 118. The deformable mirror 118, which is available as model no.
RX-170407-CTM from Xinetics, Inc., is conjugate with the pupil of the eye 100 and will be deformed to compensate for the wave abenution of the eye. The defonmable mirror 118 contains an aluminized glass faceplate with 37 actuators mounted in a square array on the back surface. Alternatively, a liquid crystal device, a micro-machined mirror, a bimorph mirror, or other suitable device could be used in place of the deformable mirror 118.
The apparatus of Fig. 1 is used as follows. The computer 150 starts the measurement process by opening the pathway of the laser beam from the laser 102. The light returning from the retina 101 is used to measure the wave aberration. The Hartmann-Shack wavefront sensor 148 provides a measurement of the eye's wave aberration, from which the deformable mirror 118 is driven to con-ect it. The process is repeated with the computer 150 generating suitable signals to cause the deformable mirror 118 to continue deforming until the RMS
error in the measured wave aberration reaches an asymptotic value, although other criteria might be used. At that point, the deformable mirroi-118 has taken the appropriate shape to provide wavefront compensation for the aberrations of the eye.
Also at that point, the final correction signal generated by the computer 150 can be provided to a contact lens fabrication system 152 used to fabricate contact lenses which would duplicate the wavefront compensation characteristics of the deformable mirror 118.
As would be obvious to those of ordinary skill in the art, such contact lenses would be custom ground for each eye for which compensation is to be provided.
Turning now to Fig. 2, there is shown in diagrammatic flow chart form the steps performed by the software resident in the computer 150 for utilizing the data obtained from the CCD device 146. At Step 1, the digital image is acquired by the computer 150 from the CCD camera. Each image consists of 512 pixels by 512 pixels at 12 bits. Then, at Step 2, the computer 1-50 computes the centroid of the spot forlned by each lenslet of the wavefront sensor. The centroid of each spot specifies its position. By comparing the positions of corresponding spots in a reference pattern and in the pattern obtained from the eye, the shifts in each focus spot in both the x and y directions can be calculated.
Next, at Step 3, the slope data are fit with the sum of the first derivatives of 65 Zernike polynomials, using a least squares procedure to determine the weight for each polynomial, similar to that discussed by Liang et al. in their report referenced above, though their method included no polynomials beyond fourth order.
Then, at Step 4, the Zernike polynomials are weighted with the coefficients calculated at Step 3. The 65 polynomials in the wavefront fit include all Zernike modes with radial power less than or equal to 10, except for the piston term. The first order Zernike modes are the linear terms. The second order modes are the quadratic terms, which correspond to the familiar aberrations, defocus, and astigmatism. The third order modes are the cubic terms, which correspond to the coma and coma-like aberrations. The fourth order modes contain spherical aberrations as well as other modes. The fifth to tenth order modes are the higher-order, irregular aberrations. Local irregularities in the wavefront within the pupil are represented by these higher-order Zernike modes.
The weighted Zernike polynomials are added together at Step 5 to obtain the reconstructed wave aberration. The wave aberratior- is evaluated at the locations of the actuators of the deformable mirror 118 to produce a correction signal at Step 6, which is then sent by the computer 150 to the wavefront compensation device which, as shown in Fig. 1, is preferably a deformable mirror 118. The feedback loop continues to receive the reconstructed wave aberration results, feeding back an appropriate correction signal until the RMS error in the reconstructed wave aberration sigrial reaches an asymptotic value. At that point, the deformable mirror 118 has been deformedl such that, when the eye looks through it, it will compensate for all of the detected aberrations of the eye 100.
As is known to those of ordinary skill in the art, spectacles and contact lenses are available to correct vision, but they only correct defocus and sometimes astigmatism in the eye. Even normal eyes have other aberrations that are not corrected by conventional spectacles or contact lenses. The wavefront sensor 1154 of the present invention is capable of automatically measuring those aberrations. Thus, using the adaptive optics system of Fig. 1 allows correction of monochromatic aberrations of the human eye beyond defocus and astigmatism. Accordingly, the adaptive optics system of Fig. 1 provides unprecedented optical quality in human eyes, both for improved vision and for providing sharper pictures of the retina.
Figs. 3a-3d are graphs of data from the wavefront sensor showing that the adaptive optics system of the present invention successfully corrects the aberrations of the eye. Figs.
3a and 3b show, for one subject, the wavefront error versus pupil position without adaptive compensation and with adaptive compensation, respectively, using the present invention. In a test in which four subjects were measured, adaptive compensation reduced the peak to valley wavefront error across a 6 mm pupil by a factor of 4, on average.
Figs. 3c and 3d show the point spread function (PSF), computed from the wave aberration, without adaptive compensation and with adaptive compensation, respectively.
Adaptive compensation increased the Strehl ratio, which is proportional to the peak intensity of the PSF, from 0.09 to 0.47. The average increase for all four eyes measured was nearly 4 fold, from 0.06 to 0.23. After compensation, the PS]F for the subject shown has a full-width at half height (F)WHH) of 2.0 microns, clcise to the value of 1.9 microns expected from diffraction alone. The present invention providles what is believed to be the best optical quality ever achieved in the human eye.
Fig. 4 is a graph of the RMS wavefront error, averaged across 4 eyes, associated with each Zernike order of the wave aberration. The RMS wavefront error is reduced by adaptive compensation for Zernike orders up to fifth order. Spectacles, contact lenses, and one previous attempt to use a deformable mirror to correct the eye's aberrations have only corrected second order aberrations (defocus and astigmatism).
Once the correction has been achieved, the apparatus of the present invention can be used to provide the subject with supernormal retinal image quality, in which case the subject views visual imagery through the deformable mirror 118. A six-fold improvement in vision, as measured with contrast sensitivity for fme gratings, for individuals looking through the present apparatus has been achieved. Individuals can see very high frequency gratings through the adaptive optics system that are above the resolution limit in normal viewing without adaptive optics.
Alternatively, once the correction has been achieved, the apparatus of the present invention shown in Fig. 1 can also be used to provide high resolution images of the retina 101. A krypton flash lamp 138 is imaged onto the eye's pupil by the lenses 134, 132, 130, and 126 and mirror 128 after passing through the beamsplitter 124. The lamp 138 delivers a 4 msec. flash, thereby illuminating a retinal disk on the retina 101 that is 1 degree in diameter. A narrow band interference filter 136 shapes the spectral output of the lamp 138.
The image of the retina 101 passes through the beamsplitter 124 and the lenses and 120, is reflected by the deformable mirror 118, which has already been shaped to compensate for the eye's aberrations, and passes through the lens 116. The light is then reflected by the mirror 114 onto the lens 140 and through an aperture 141, where the reflected image is focused by the lens 142 onto the CCD device 145. The electrical signals corresponding to the light captured by the CCD camera 145 may be acquired in a manner similar to the light acquisition system which acquires the data from the CCD
camera 146 and then be stored for later use in the computer 150. The images may then be shown on a monitor (not shown) connected to the computer 150 and/or sent to a suitable printing device (not shown) connected to the computer 150.
Using the apparatus of the present invention, single cells in the living human retina have been routinely resolved for the first time. The adaptive optic system of the present invention provides a non-invasive technique with which to study the normal and pathological living retina at a microscopic spatial scale. The theoretical limit of the transverse resolution of fundus imaging is proportional to the diameter of the dilated pupil. If adaptive compensation were complete for an 8 mm pupil, for example, the transverse resolution would be increased 3.2 times over that for a 2.5 mm pupil, a typical pupil diameter used by currently available fundus cameras.
The axial resolution, which is critical in optical in-depth sectioning of the retina, grows as the square of the pupil diameter. Therefore, complete adaptive compensation across an 8 mm pupil could theoretically increase the axial resolution of a confocal ophthalmoscope by a factor of 10 over an instrument with a 2.5 mm exit pupil. The full-width at half-height (FWHH) of the PSF in depth is 27 microns, which approaches that of optical coherence tomography, but provides the additional advantage of high transverse resolution not possible with optical coherence tomography alone.
The success of the apparatus of the present invention establishes that it can also be used to improve vision by reshaping the eye's optics, as in laser refractive surgery, or by fabricating customized optical elements such as contact lenses or intraocular lenses. As shown, Figs. 1 and 2, the final correction signal can be provided to a contact lens or intraocular lens fabrication system or laser refractive surgical procedure 152 instead of the deformable mirror 118. As would be obvious to those of ordinary skill in the art, such contact lenses, intraocular lenses, or surgical correction would be customized for each eye for which compensation is to be provided. Additional aberrations besides defocus and astigmatism could be corrected with either an open or a closed loop system.
The invention described herein allows for the first complete description of the aberrations of the human eye combined with a demonstrated method to correct these aberrations. The applications of the present invention are four-fold. First, the invention can be utilized to provide a more accurate measure of the aberrations of the unaided eye. Second, the present invention can be used to evaluate the ber.Lefit of various techniques to correct the aberrations of the eye, such as custom glasses, custom contact lenses, and surgical procedures.
Third, the present invention can be used to improve vision in optical instruments such as telescopes and binoculars, custom glasses, custom contact lenses, and with surgical procedures such as photorefractive keratectomy (PRK). Fourth, the invention can be utilized to improve the axial and transverse resolution of images of the living retina.
Current fundus cameras suffer from the problem that, in tht prior art, the aberrations of the eye limit its resolution, a limit that has remained since the invention of the ophthalmoscope.
Although only a preferred embodiment is specifically illustrated and described herein, it will be appreciated that many modifications and vairiations of the present invention are possible in light of the above teachings and within the purview of the appended claims without departing from the spirit and intended scope of the invention.
*rB
In view of the foregoing, it is apparent that there exists a need in the art for a method of and an apparatus for producing ophthalmic optical elements that provide improved or supernormal vision over that which is currently avail[able, as well as high resolution retinal images. It is, therefore, a primary object of the present invention to provide a method of and an apparatus for accurately measuring higher order aberrations of the eye and for using the data thus measured to compensate for those aberrations with a customized optical element.
It is also an object of the present invention to provide an improved wavefront sensor which rejects light reflected from structures other than the retina and which is capable of providing a complete measurement of the eye's aberrations.
It is a further object of the present invention to utilize such an improved wavefront sensor in combination with a deformable mirror to correct the wave aberration in a feedback manner such that the subject achieves normal or supernormal vision.
It is likewise a primary object of the present invention to provide a method of and an apparatus for producing high resolution retinal images which allow the imaging of microscopic structures the size of single cells in a human retina.
Briefly described, these and other objects of the invention are accomplished by providing a system for receiving light reflected from a retina of an eye. The wavefront in the plane of the pupil is recreated in the plane of a lenslet array of a Hartmann-Shack wavefront sensor. Each of the lenslets in the lenslet array is used to form an aerial image of the retinal point source on a CCD camera located adjacent to the lenslet array. The wave aberration of the eye, in the form of a point source produced on the retina by a laser beam, displaces each spot by an amount proportional to the local slope of the wavefront at each of the lenslets. The output from the digital CCD camera is sent to a computer which then calculates the wave aberration and provides a signal to a deformable mirror. Following an iterative procedure, the deformable mirror ultimately acquires a shape that is identical to the wave aberration measured at the outset, but with half the ainplitude. This deformation is the appropriate one to flatten the distorted wavefront into a plane wave, which improves image quality.
In its method aspects, the system of the present invention, using the computer, first acquires the CCD image, as described above. Then, the computer computes the centroid of the spot formed by each of the lenslets of the wavefcont sensor. Shifts in each focus spot in the x and y directions are calculated and then used as the slope data to fit with the sum of the first derivatives of 65 Zernike polynomials, using a least squares procedure, to determine the weight for each polynomial.
Then, the Zemike polynomials are weighted with the calculated coefficients.
The 65 polynomials in the wavefront fit include all Zemike modes with radial power less than or equal to 10, except for the piston term.
The weighted Zemike polynomials are then added together, to result in the reconstructed wave aberration. The wave aberration is then evaluated at the locations of the actuators of a deformable mirror in order to produce the correction signal which is sent by the computer to the wavefront compensation device or deformable mirror, as discussed above.
Such a feedback loop continues to receive the reconstructed wave aberration results, feeding back an appropriate correction signal, until the RMS of the reconstructed wave aberration signal reaches an asymptotic value, at which point, the deformable mirror has been deformed such that it will compensate for all the detected aberrations of the eye.
When the reconstructed wave aberration sigr.ial reaches its asymptotic value, the final aberration signal (including all of the previously genierated signals up until the RMS error reaches the asymptotic value) can be used to produae. contact lenses to correct for all of the monochromatic aberrations of the human eye or for surgical procedures.
The present invention can also be used to provide high resolution images of the retina.
The system for producing such images uses a krypton flash lamp which is designed to illuminate a retinal disk to provide an image of the retina which is reflected by the deformable mirror onto a lens and through an aperture such that the reflected image of the retina is focused onto a second CCD camera. The signals generated by the camera are acquired in a manner similar to that described above in connectiori with the first CCD
camera and are stored for later use in the computer.
With these and other objects, advantages, and features of the invention that may become hereinafter apparent, the nature of the invention may be more clearly understood by reference to the following detailed description of the invention, the appended claims and to the drawings attached herein.
BRIEF DESCRIPTION OF THE DRAWINGS
Fig. 1 is a schematic diagram of the system of the present invention;
Fig. 2 is a diagram of a flow chart of a method for the present invention for use in fabricating contact lenses or providing retinal images using the apparatus shown in Fig. 1;
Figs. 3a-3d show the wave aberration and the corresponding point spread functions before and after adaptive compensation using the system of the present invention, respectively; and, Fig. 4 shows the Zernike decomposition of the wave aberration of the eye before and after adaptive compensation, showing that the invention can correct not only second order aberrations (defocus and astigmatism) but also high=-order aberrations.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT
Referring now to Fig. 1, there is shown, in schematic diagram form, the apparatus of the present invention which can be used to both improve visual performance and to provide high resolution retinal images of eyes. The apparatus of the present invention, as shown in Fig. 1, measures the aberrations of the eye using a Hartmann-Shack wavefront sensor and then corrects them in a closed feedback loop with a compensating optical component such as a deformable mirror.
To measure the eye's wave aberration, a point source is produced on the retina by a laser 102. The light from the laser 102, is controlleci by a shutter (not shown). The laser light passes through a spatial filter 104 and is collimated by an achromatic doublet lens 106. The collimated laser beam is reflected by the polarizing 'beamsplitter 110, passes through the lenses 112 and 116, and is incident onto a deformable mirror 118. The laser beam reflected from the deformable mirror 118 is focused by the lens 120, passes through the lens 122 and the second beamsplitter 124 and reaches the eye 100 at a diameter of about 1.5 mm at the pupil. The lens of the eye 100 focuses the laser beain on its retina 101.
Possible myopia or hyperopia of the tested eye is corrected by movemetit of the eye 100 and the lens 122 with respect to the lens 120.
The light reflected from the retina 101 forms a distorted wavefront at the pupil, which is recreated in the plane of the deformable mirror 118 by the lenses 122 and 120, and also in the plane of the lenslet array of a Hartmann-Shack viiavefront sensor 148 by the lenses 116 and 112. The pupil is conjugate with a two-dimensional array of lenslets 148.
Each of the lenslets in the array 148 forms an aerial image of the retinal point source on the CCD camera 146. The CCD camera 146 sends the digitized image to the computer 150 where it is stored in RAM or on magnetic or other storage media.
Aberrations displace each spot by an amount proportional to the local slope of the wavefront at each lenslet. The slope of the wavefroiit can be determined from the displacement of these spots relative to a known aberration-free reference. The wavefront sensor 154 measures the local slopes in both the x and y directions at 2171ocations simultaneously across the dilated pupil. From the array of slopes, the wave aberration is reconstructed as described later herein.
The beamsplitter 110 which forms part of the wavefront sensor 154 is preferably configured as a polarizing beamsplitter in order to remove unwanted light reflected from the first surface of the comea of the eye 100 and other optical elements, such as lenses 112, 116, 120, and 122. Such light would otherwise interfere with the operation of the wavefront sensor 154 and would make automatic procedures for measuring the wave aberration more difficult.
The wavefront sensor 154 of the present invention provides a much more complete measurement of the aberrations of the eye than has been possible before in part because a large number of samples in the pupil of the eye are used. Using the apparatus of the present invention, it has been found that the eye 100 contains complex abeffations that are not corrected by spectacles or contact lenses, and that such aberrations are significant when the pupil is large. Even aberrations of order 5 and greater, which the present wavefront sensor 154 is the first to measure, has significant impact on the eye's optical quality. Moreover, the higher order aberrations are stable over time. Such stability is important because it shows that the aberrations can be corrected using a static optical corrector, such as a custom-made contact lens.
Once the wave aberration is measured, as described above, it is compensated with a device conjugate with the pupil of the eye 100 that can control the phase of the light at different points in the pupil. As will be further described in detail in connection with Fig. 2, the computer 150, under software control, produces a correction signal which is fed back to the defonmable mirror 118. The deformable mirror 118, which is available as model no.
RX-170407-CTM from Xinetics, Inc., is conjugate with the pupil of the eye 100 and will be deformed to compensate for the wave abenution of the eye. The defonmable mirror 118 contains an aluminized glass faceplate with 37 actuators mounted in a square array on the back surface. Alternatively, a liquid crystal device, a micro-machined mirror, a bimorph mirror, or other suitable device could be used in place of the deformable mirror 118.
The apparatus of Fig. 1 is used as follows. The computer 150 starts the measurement process by opening the pathway of the laser beam from the laser 102. The light returning from the retina 101 is used to measure the wave aberration. The Hartmann-Shack wavefront sensor 148 provides a measurement of the eye's wave aberration, from which the deformable mirror 118 is driven to con-ect it. The process is repeated with the computer 150 generating suitable signals to cause the deformable mirror 118 to continue deforming until the RMS
error in the measured wave aberration reaches an asymptotic value, although other criteria might be used. At that point, the deformable mirroi-118 has taken the appropriate shape to provide wavefront compensation for the aberrations of the eye.
Also at that point, the final correction signal generated by the computer 150 can be provided to a contact lens fabrication system 152 used to fabricate contact lenses which would duplicate the wavefront compensation characteristics of the deformable mirror 118.
As would be obvious to those of ordinary skill in the art, such contact lenses would be custom ground for each eye for which compensation is to be provided.
Turning now to Fig. 2, there is shown in diagrammatic flow chart form the steps performed by the software resident in the computer 150 for utilizing the data obtained from the CCD device 146. At Step 1, the digital image is acquired by the computer 150 from the CCD camera. Each image consists of 512 pixels by 512 pixels at 12 bits. Then, at Step 2, the computer 1-50 computes the centroid of the spot forlned by each lenslet of the wavefront sensor. The centroid of each spot specifies its position. By comparing the positions of corresponding spots in a reference pattern and in the pattern obtained from the eye, the shifts in each focus spot in both the x and y directions can be calculated.
Next, at Step 3, the slope data are fit with the sum of the first derivatives of 65 Zernike polynomials, using a least squares procedure to determine the weight for each polynomial, similar to that discussed by Liang et al. in their report referenced above, though their method included no polynomials beyond fourth order.
Then, at Step 4, the Zernike polynomials are weighted with the coefficients calculated at Step 3. The 65 polynomials in the wavefront fit include all Zernike modes with radial power less than or equal to 10, except for the piston term. The first order Zernike modes are the linear terms. The second order modes are the quadratic terms, which correspond to the familiar aberrations, defocus, and astigmatism. The third order modes are the cubic terms, which correspond to the coma and coma-like aberrations. The fourth order modes contain spherical aberrations as well as other modes. The fifth to tenth order modes are the higher-order, irregular aberrations. Local irregularities in the wavefront within the pupil are represented by these higher-order Zernike modes.
The weighted Zernike polynomials are added together at Step 5 to obtain the reconstructed wave aberration. The wave aberratior- is evaluated at the locations of the actuators of the deformable mirror 118 to produce a correction signal at Step 6, which is then sent by the computer 150 to the wavefront compensation device which, as shown in Fig. 1, is preferably a deformable mirror 118. The feedback loop continues to receive the reconstructed wave aberration results, feeding back an appropriate correction signal until the RMS error in the reconstructed wave aberration sigrial reaches an asymptotic value. At that point, the deformable mirror 118 has been deformedl such that, when the eye looks through it, it will compensate for all of the detected aberrations of the eye 100.
As is known to those of ordinary skill in the art, spectacles and contact lenses are available to correct vision, but they only correct defocus and sometimes astigmatism in the eye. Even normal eyes have other aberrations that are not corrected by conventional spectacles or contact lenses. The wavefront sensor 1154 of the present invention is capable of automatically measuring those aberrations. Thus, using the adaptive optics system of Fig. 1 allows correction of monochromatic aberrations of the human eye beyond defocus and astigmatism. Accordingly, the adaptive optics system of Fig. 1 provides unprecedented optical quality in human eyes, both for improved vision and for providing sharper pictures of the retina.
Figs. 3a-3d are graphs of data from the wavefront sensor showing that the adaptive optics system of the present invention successfully corrects the aberrations of the eye. Figs.
3a and 3b show, for one subject, the wavefront error versus pupil position without adaptive compensation and with adaptive compensation, respectively, using the present invention. In a test in which four subjects were measured, adaptive compensation reduced the peak to valley wavefront error across a 6 mm pupil by a factor of 4, on average.
Figs. 3c and 3d show the point spread function (PSF), computed from the wave aberration, without adaptive compensation and with adaptive compensation, respectively.
Adaptive compensation increased the Strehl ratio, which is proportional to the peak intensity of the PSF, from 0.09 to 0.47. The average increase for all four eyes measured was nearly 4 fold, from 0.06 to 0.23. After compensation, the PS]F for the subject shown has a full-width at half height (F)WHH) of 2.0 microns, clcise to the value of 1.9 microns expected from diffraction alone. The present invention providles what is believed to be the best optical quality ever achieved in the human eye.
Fig. 4 is a graph of the RMS wavefront error, averaged across 4 eyes, associated with each Zernike order of the wave aberration. The RMS wavefront error is reduced by adaptive compensation for Zernike orders up to fifth order. Spectacles, contact lenses, and one previous attempt to use a deformable mirror to correct the eye's aberrations have only corrected second order aberrations (defocus and astigmatism).
Once the correction has been achieved, the apparatus of the present invention can be used to provide the subject with supernormal retinal image quality, in which case the subject views visual imagery through the deformable mirror 118. A six-fold improvement in vision, as measured with contrast sensitivity for fme gratings, for individuals looking through the present apparatus has been achieved. Individuals can see very high frequency gratings through the adaptive optics system that are above the resolution limit in normal viewing without adaptive optics.
Alternatively, once the correction has been achieved, the apparatus of the present invention shown in Fig. 1 can also be used to provide high resolution images of the retina 101. A krypton flash lamp 138 is imaged onto the eye's pupil by the lenses 134, 132, 130, and 126 and mirror 128 after passing through the beamsplitter 124. The lamp 138 delivers a 4 msec. flash, thereby illuminating a retinal disk on the retina 101 that is 1 degree in diameter. A narrow band interference filter 136 shapes the spectral output of the lamp 138.
The image of the retina 101 passes through the beamsplitter 124 and the lenses and 120, is reflected by the deformable mirror 118, which has already been shaped to compensate for the eye's aberrations, and passes through the lens 116. The light is then reflected by the mirror 114 onto the lens 140 and through an aperture 141, where the reflected image is focused by the lens 142 onto the CCD device 145. The electrical signals corresponding to the light captured by the CCD camera 145 may be acquired in a manner similar to the light acquisition system which acquires the data from the CCD
camera 146 and then be stored for later use in the computer 150. The images may then be shown on a monitor (not shown) connected to the computer 150 and/or sent to a suitable printing device (not shown) connected to the computer 150.
Using the apparatus of the present invention, single cells in the living human retina have been routinely resolved for the first time. The adaptive optic system of the present invention provides a non-invasive technique with which to study the normal and pathological living retina at a microscopic spatial scale. The theoretical limit of the transverse resolution of fundus imaging is proportional to the diameter of the dilated pupil. If adaptive compensation were complete for an 8 mm pupil, for example, the transverse resolution would be increased 3.2 times over that for a 2.5 mm pupil, a typical pupil diameter used by currently available fundus cameras.
The axial resolution, which is critical in optical in-depth sectioning of the retina, grows as the square of the pupil diameter. Therefore, complete adaptive compensation across an 8 mm pupil could theoretically increase the axial resolution of a confocal ophthalmoscope by a factor of 10 over an instrument with a 2.5 mm exit pupil. The full-width at half-height (FWHH) of the PSF in depth is 27 microns, which approaches that of optical coherence tomography, but provides the additional advantage of high transverse resolution not possible with optical coherence tomography alone.
The success of the apparatus of the present invention establishes that it can also be used to improve vision by reshaping the eye's optics, as in laser refractive surgery, or by fabricating customized optical elements such as contact lenses or intraocular lenses. As shown, Figs. 1 and 2, the final correction signal can be provided to a contact lens or intraocular lens fabrication system or laser refractive surgical procedure 152 instead of the deformable mirror 118. As would be obvious to those of ordinary skill in the art, such contact lenses, intraocular lenses, or surgical correction would be customized for each eye for which compensation is to be provided. Additional aberrations besides defocus and astigmatism could be corrected with either an open or a closed loop system.
The invention described herein allows for the first complete description of the aberrations of the human eye combined with a demonstrated method to correct these aberrations. The applications of the present invention are four-fold. First, the invention can be utilized to provide a more accurate measure of the aberrations of the unaided eye. Second, the present invention can be used to evaluate the ber.Lefit of various techniques to correct the aberrations of the eye, such as custom glasses, custom contact lenses, and surgical procedures.
Third, the present invention can be used to improve vision in optical instruments such as telescopes and binoculars, custom glasses, custom contact lenses, and with surgical procedures such as photorefractive keratectomy (PRK). Fourth, the invention can be utilized to improve the axial and transverse resolution of images of the living retina.
Current fundus cameras suffer from the problem that, in tht prior art, the aberrations of the eye limit its resolution, a limit that has remained since the invention of the ophthalmoscope.
Although only a preferred embodiment is specifically illustrated and described herein, it will be appreciated that many modifications and vairiations of the present invention are possible in light of the above teachings and within the purview of the appended claims without departing from the spirit and intended scope of the invention.
*rB
Claims (25)
1. A wavefront sensor for determining wave aberrations of a living eye, said wavefront sensor receiving a reflected point source image of the retina of said eye, comprising:
a plurality of lenslets which form a lenslet array for receiving said reflected point source image of said retina and for creating an aerial image of the retinal point source;
said lenslet array being configured such that it is capable of providing resolution for at least fifth order aberrations;
a camera located adjacent to said lenslet array for viewing said aerial image of the retinal point source formed on each of said plurality of lenslets of said lenslet array; and a digital data processor connected to receive video output signals from said camera and for converting said video output signals to digital signals representative of said retinal point source aerial images, said digital data processor further calculating the wave aberrations of said eye so as to include at least fifth order modes, using said representative digital signals.
a plurality of lenslets which form a lenslet array for receiving said reflected point source image of said retina and for creating an aerial image of the retinal point source;
said lenslet array being configured such that it is capable of providing resolution for at least fifth order aberrations;
a camera located adjacent to said lenslet array for viewing said aerial image of the retinal point source formed on each of said plurality of lenslets of said lenslet array; and a digital data processor connected to receive video output signals from said camera and for converting said video output signals to digital signals representative of said retinal point source aerial images, said digital data processor further calculating the wave aberrations of said eye so as to include at least fifth order modes, using said representative digital signals.
2. The wavefront sensor of claim 1, further including a polarizer through which said reflected point source image of said retina passes prior to being received by said plurality of lenslets.
3. The wavefront sensor of claim 1, further including a compensating optical device connected to said digital data processor, such that, under control of said digital data processor, said compensating optical device is adjusted for providing wavefront compensation for said wave aberrations of said eye.
4. The wavefront sensor of claim 3, further including a polarizer filter through which said reflected point source image of said retina passes prior to being received by said plurality of lenslets.
5. The wavefront sensor of claim 1, wherein said lenslet array is capable of providing resolution of up to at least tenth order wave aberrations.
6. The wavefront sensor of claim 1, wherein said lenslet array is a Hartmann-Shack wavefront sensor having up to 217 lenslets.
7. The wavefront sensor of claim 1, further including at least one of a contact and intraocular lens fabrication system connected to receive the calculated wave aberrations from said digital data processor for fabricating at least one contact or intraocular lens to provide wavefront compensation for said wave aberrations of said living eye.
8. The wavefront sensor of claim 1, further including surgical equipment connected to receive the calculated wave aberrations from said digital data processor for use in performing surgery on said living eye to provide wavefront compensation for said wave aberrations of said living eye.
9. The apparatus of claim 3, wherein said compensating optical device is one of a deformable mirror, liquid crystal device, micro-machined mirror and bimorph mirror.
10. Apparatus for fabricating contact or intraocular lenses to correct for at least third order wave aberrations of a living eye, comprising;
means for generating a reflected point source image of a retina of said living eye;
means for receiving said reflected point source image and for converting said point source image to corresponding digital signals;
a digital data processor for calculating wave aberrations of the eye so as to include at least third order modes, using said digital signals; and at least one of a contact lens and intraocular fabrication system connected to receive the calculated wave aberrations from said digital data processor for fabricating at least one contact or intraocular lens to provide wavefront compensation for said at least third order wave aberrations of said living eye.
means for generating a reflected point source image of a retina of said living eye;
means for receiving said reflected point source image and for converting said point source image to corresponding digital signals;
a digital data processor for calculating wave aberrations of the eye so as to include at least third order modes, using said digital signals; and at least one of a contact lens and intraocular fabrication system connected to receive the calculated wave aberrations from said digital data processor for fabricating at least one contact or intraocular lens to provide wavefront compensation for said at least third order wave aberrations of said living eye.
11. The apparatus of claim 10, wherein said means for generating comprises a plurality of lenslets which form a lenslet array for receiving said reflected point source image of said retina, said lenslet array being configured such that it is capable of providing resolution for at least third order aberrations.
12. The apparatus of claim 10, further including a polarizing filter through which said reflected point source image of said retina passes prior to being received by said means for receiving said reflected point source.
13. A method for fabricating contact lenses to correct at least third order wave aberrations of a living eye, comprising the steps of:
generating a reflected point source image of the retina of said living eye;
receiving said reflected point source image and converting said point source image to corresponding digital signals;
calculating wave aberrations of said eye so as to include at least third order modes, using said digital signals; and receiving the calculated wave aberrations for fabricating at least one contact lens to provide wavefront compensation for said at least third order wave aberrations of said living eye.
generating a reflected point source image of the retina of said living eye;
receiving said reflected point source image and converting said point source image to corresponding digital signals;
calculating wave aberrations of said eye so as to include at least third order modes, using said digital signals; and receiving the calculated wave aberrations for fabricating at least one contact lens to provide wavefront compensation for said at least third order wave aberrations of said living eye.
14. The method of claim 13, further including the step of polarizing said reflected point source image to remove stray light reflected from the cornea of said living eye prior to receiving said reflected point source image.
15. A method for determining wave aberrations of a living eye using a wavefront sensor which receives a reflected point source image of the retina of said eye, comprising the steps of:
providing a plurality of lenslets which form a lenslet array for receiving said reflected point source image of said retina, said lenslet array being configured such that it is capable of providing resolution for at least fifth order aberrations;
receiving an aerial image of the retinal point source formed on each of said plurality of lenslets of said lenslet array and generating signals representative thereof; and converting said signals to digital signals representative of said retinal point source aerial images, and calculating wave aberrations of said eye so as to include at least fifth order modes, using said representative digital signals.
providing a plurality of lenslets which form a lenslet array for receiving said reflected point source image of said retina, said lenslet array being configured such that it is capable of providing resolution for at least fifth order aberrations;
receiving an aerial image of the retinal point source formed on each of said plurality of lenslets of said lenslet array and generating signals representative thereof; and converting said signals to digital signals representative of said retinal point source aerial images, and calculating wave aberrations of said eye so as to include at least fifth order modes, using said representative digital signals.
16. The method of claim 15, further including the step of polarizing said reflected point source image to remove stray light reflected from the cornea of said living eye prior to said plurality of lenslets receiving said reflected point source image.
17. A method for determining wave aberrations of a living eye using a wavefront sensor which receives a reflected point source image of the retina of said eye, comprising the steps of:
providing a plurality of lenslets which form a lenslet array for receiving said reflected point source image of said retina, said lenslet array being configured such that it is capable of providing resolution for at least third order aberrations;
receiving an aerial image of the retinal point source formed on each of said plurality of lenslets of said lenslet array and generating signals representative thereof;
converting said signals to digital signals representative of said retinal point source aerial images, and calculating wave aberrations of said eye so as to include at least third order modes, using said representative digital signals; and adjusting a compensating optical device to provide wavefront compensation for said wave aberrations of said living eye using said calculated at least third order wave aberrations of said living eye.
providing a plurality of lenslets which form a lenslet array for receiving said reflected point source image of said retina, said lenslet array being configured such that it is capable of providing resolution for at least third order aberrations;
receiving an aerial image of the retinal point source formed on each of said plurality of lenslets of said lenslet array and generating signals representative thereof;
converting said signals to digital signals representative of said retinal point source aerial images, and calculating wave aberrations of said eye so as to include at least third order modes, using said representative digital signals; and adjusting a compensating optical device to provide wavefront compensation for said wave aberrations of said living eye using said calculated at least third order wave aberrations of said living eye.
18. Apparatus for generating high resolution images of the retina of a living eye, comprising:
means for generating a reflected point source image of the retina of said living eye;
means for receiving said reflected point source image and for converting said point source image to corresponding digital signals;
a digital data processor for calculating at least third order wave aberrations using said digital signals;
means for illuminating a retinal disk on said living eye for producing a retinal disk image;
a compensating optical device for reflecting said retinal disk image, said compensating optical device being adjusted using said calculated wave aberrations such that wavefront compensation for said wave aberrations is provided for said living eye; and means for providing an image of said reflected retinal disk image after its reflection by said compensating optical device.
means for generating a reflected point source image of the retina of said living eye;
means for receiving said reflected point source image and for converting said point source image to corresponding digital signals;
a digital data processor for calculating at least third order wave aberrations using said digital signals;
means for illuminating a retinal disk on said living eye for producing a retinal disk image;
a compensating optical device for reflecting said retinal disk image, said compensating optical device being adjusted using said calculated wave aberrations such that wavefront compensation for said wave aberrations is provided for said living eye; and means for providing an image of said reflected retinal disk image after its reflection by said compensating optical device.
19. The apparatus of claim 18, wherein said compensating optical device is one of a deformable mirror, liquid crystal device, micro-machined mirror and bimorph mirror.
20. The apparatus of claim 18, wherein said means for generating comprises a plurality of lenslets which form a lenslet array for receiving said reflected point source image of said retina, said lenslet array being configured such that it is capable of providing resolution for at least third order aberrations.
21. The apparatus of claim 20, further including a polarizer through which said reflected point source image of said retina passes prior to being received by said plurality of lenslets.
22. An optical instrument which incorporates a wavefront sensor for determining wave aberrations of a living eye, said wavefront sensor receiving a reflected point source image of the retina of said eye, comprising:
a plurality of lenslets which form a lenslet array for receiving said reflected point source image of said retina and for creating an aerial image of the retinal point source;
said lenslet array being configured such that it is capable of providing resolution for at least fifth order aberrations;
a camera located adjacent to said lenslet array for viewing said aerial image of the retinal point source formed on each of said plurality of lenslets of said lenslet array; and a digital data processor connected to receive video output signals from said camera and for converting said video output signals to digital signals representative of said retinal point source aerial images, said digital data processor further calculating the wave aberrations of said eye so as to include at least third order modes, using said representative digital signals, such that improved vision results when said living eye utilizes said optical instrument.
a plurality of lenslets which form a lenslet array for receiving said reflected point source image of said retina and for creating an aerial image of the retinal point source;
said lenslet array being configured such that it is capable of providing resolution for at least fifth order aberrations;
a camera located adjacent to said lenslet array for viewing said aerial image of the retinal point source formed on each of said plurality of lenslets of said lenslet array; and a digital data processor connected to receive video output signals from said camera and for converting said video output signals to digital signals representative of said retinal point source aerial images, said digital data processor further calculating the wave aberrations of said eye so as to include at least third order modes, using said representative digital signals, such that improved vision results when said living eye utilizes said optical instrument.
23. A method for generating high resolution images of the retina of a living eye, comprising the steps of generating a reflected point source image of the retina of said living eye;
receiving said reflected point source image and for converting said point source image to corresponding digital signals;
calculating at least third order wave aberrations using said digital signals;
illuminating a retinal disk on said living eye for producing a retinal disk image; and reflecting said retinal disk image on a compensating optical device, said compensating optical device being adjusted such that wavefront compensation for said wave aberrations is provided for said living eye.
receiving said reflected point source image and for converting said point source image to corresponding digital signals;
calculating at least third order wave aberrations using said digital signals;
illuminating a retinal disk on said living eye for producing a retinal disk image; and reflecting said retinal disk image on a compensating optical device, said compensating optical device being adjusted such that wavefront compensation for said wave aberrations is provided for said living eye.
24. The method of claim 23, further including the step of polarizing said reflected point source image to remove stray light reflected from the cornea of said living eye prior to receiving said reflected point source image.
25. Apparatus for generating high resolution images of the retina of a living eye, comprising:
means for determining at least a third order wave aberration of said living eye and for generating a correction signal representative thereof;
a compensating optical device for reflecting an image of said retina and for receiving said correction signal, said compensating optical device being adjusted using said correction signal such that wavefront compensation for said at least third order wave aberration is provided for said living eye; and means for providing said high resolution image of said retina after its reflection by said compensating optical device.
means for determining at least a third order wave aberration of said living eye and for generating a correction signal representative thereof;
a compensating optical device for reflecting an image of said retina and for receiving said correction signal, said compensating optical device being adjusted using said correction signal such that wavefront compensation for said at least third order wave aberration is provided for said living eye; and means for providing said high resolution image of said retina after its reflection by said compensating optical device.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US08/772,977 | 1996-12-23 | ||
| US08/772,977 US5777719A (en) | 1996-12-23 | 1996-12-23 | Method and apparatus for improving vision and the resolution of retinal images |
| PCT/US1997/023863 WO1998027863A1 (en) | 1996-12-23 | 1997-12-23 | Apparatus for improving vision and resolution of retinal images |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2275762A1 CA2275762A1 (en) | 1998-07-02 |
| CA2275762C true CA2275762C (en) | 2009-11-24 |
Family
ID=25096791
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002275762A Expired - Lifetime CA2275762C (en) | 1996-12-23 | 1997-12-23 | Apparatus for improving vision and resolution of retinal images |
Country Status (9)
| Country | Link |
|---|---|
| US (10) | US5777719A (en) |
| EP (1) | EP0969760B1 (en) |
| JP (1) | JP4105237B2 (en) |
| CN (1) | CN1184926C (en) |
| BR (1) | BR9714178B1 (en) |
| CA (1) | CA2275762C (en) |
| DE (1) | DE69739629D1 (en) |
| HK (1) | HK1024157A1 (en) |
| WO (1) | WO1998027863A1 (en) |
Families Citing this family (580)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5980513A (en) | 1994-04-25 | 1999-11-09 | Autonomous Technologies Corp. | Laser beam delivery and eye tracking system |
| US6271914B1 (en) | 1996-11-25 | 2001-08-07 | Autonomous Technologies Corporation | Objective measurement and correction of optical systems using wavefront analysis |
| US20010041884A1 (en) * | 1996-11-25 | 2001-11-15 | Frey Rudolph W. | Method for determining and correcting vision |
| US5777719A (en) | 1996-12-23 | 1998-07-07 | University Of Rochester | Method and apparatus for improving vision and the resolution of retinal images |
| EP0910986A1 (en) * | 1997-10-24 | 1999-04-28 | BRITISH TELECOMMUNICATIONS public limited company | Imaging apparatus |
| US6547395B1 (en) * | 1998-02-06 | 2003-04-15 | Wavefront Sciences, Inc. | Methods of measuring moving objects and reducing exposure during wavefront measurements |
| ES2277430T3 (en) * | 1998-03-04 | 2007-07-01 | Visx Incorporated | LASER PRESBORAGE TREATMENT SYSTEM. |
| US6007204A (en) * | 1998-06-03 | 1999-12-28 | Welch Allyn, Inc. | Compact ocular measuring system |
| US6598975B2 (en) * | 1998-08-19 | 2003-07-29 | Alcon, Inc. | Apparatus and method for measuring vision defects of a human eye |
| DE69902549T2 (en) | 1998-08-19 | 2003-04-17 | Alcon, Inc. | DEVICE AND METHOD FOR MEASURING DEFECTIVES OF A HUMAN EYE |
| CN101596096B (en) * | 1998-12-10 | 2015-11-25 | 卡尔蔡斯耶拿有限公司 | Heed contacted measure eyes axial length and/or corneal curvature and/or anterior chamber depth, the especially device measured of IOL |
| US6450642B1 (en) | 1999-01-12 | 2002-09-17 | California Institute Of Technology | Lenses capable of post-fabrication power modification |
| DE19904753C1 (en) | 1999-02-05 | 2000-09-07 | Wavelight Laser Technologie Gm | Device for photorefractive corneal surgery of the eye for correcting high-order visual defects |
| FR2791548B1 (en) * | 1999-04-01 | 2001-07-06 | Univ Paris Vii Denis Diderot | DEVICE FOR OBSERVING A HIGH RESOLUTION BODY |
| US6857741B2 (en) * | 2002-01-16 | 2005-02-22 | E-Vision, Llc | Electro-active multi-focal spectacle lens |
| US6050687A (en) * | 1999-06-11 | 2000-04-18 | 20/10 Perfect Vision Optische Geraete Gmbh | Method and apparatus for measurement of the refractive properties of the human eye |
| US6986579B2 (en) * | 1999-07-02 | 2006-01-17 | E-Vision, Llc | Method of manufacturing an electro-active lens |
| US6733130B2 (en) | 1999-07-02 | 2004-05-11 | E-Vision, Llc | Method for refracting and dispensing electro-active spectacles |
| US6619799B1 (en) | 1999-07-02 | 2003-09-16 | E-Vision, Llc | Optical lens system with electro-active lens having alterably different focal lengths |
| US6871951B2 (en) * | 2000-06-23 | 2005-03-29 | E-Vision, Llc | Electro-optic lens with integrated components |
| US6491391B1 (en) * | 1999-07-02 | 2002-12-10 | E-Vision Llc | System, apparatus, and method for reducing birefringence |
| US7023594B2 (en) * | 2000-06-23 | 2006-04-04 | E-Vision, Llc | Electro-optic lens with integrated components |
| US6517203B1 (en) | 1999-07-02 | 2003-02-11 | E-Vision, Llc | System, apparatus, and method for correcting vision using electro-active spectacles |
| US6491394B1 (en) | 1999-07-02 | 2002-12-10 | E-Vision, Llc | Method for refracting and dispensing electro-active spectacles |
| EP1060703A3 (en) * | 1999-06-16 | 2002-06-05 | 20/10 Perfect Vision Optische Geraete GmbH | Method and apparatus for precompensating the refractive properties of the human eye with adaptive optical feedback control |
| US7264354B2 (en) * | 1999-07-02 | 2007-09-04 | E-Vision, Llc | Method and apparatus for correcting vision using an electro-active phoropter |
| US20070258039A1 (en) * | 1999-07-02 | 2007-11-08 | Duston Dwight P | Spectacle frame bridge housing electronics for electro-active spectacle lenses |
| US7988286B2 (en) | 1999-07-02 | 2011-08-02 | E-Vision Llc | Static progressive surface region in optical communication with a dynamic optic |
| US7404636B2 (en) * | 1999-07-02 | 2008-07-29 | E-Vision, Llc | Electro-active spectacle employing modal liquid crystal lenses |
| US6851805B2 (en) * | 1999-07-02 | 2005-02-08 | E-Vision, Llc | Stabilized electro-active contact lens |
| US7290875B2 (en) * | 2004-11-02 | 2007-11-06 | Blum Ronald D | Electro-active spectacles and method of fabricating same |
| US7775660B2 (en) * | 1999-07-02 | 2010-08-17 | E-Vision Llc | Electro-active ophthalmic lens having an optical power blending region |
| US7290876B2 (en) * | 1999-07-02 | 2007-11-06 | E-Vision, Llc | Method and system for electro-active spectacle lens design |
| US7604349B2 (en) * | 1999-07-02 | 2009-10-20 | E-Vision, Llc | Static progressive surface region in optical communication with a dynamic optic |
| US20090103044A1 (en) * | 1999-07-02 | 2009-04-23 | Duston Dwight P | Spectacle frame bridge housing electronics for electro-active spectacle lenses |
| EP1119324A1 (en) * | 1999-08-11 | 2001-08-01 | Asclepion-Meditec AG | Method and device for completely correcting visual defects of the human eye |
| US6305802B1 (en) | 1999-08-11 | 2001-10-23 | Johnson & Johnson Vision Products, Inc. | System and method of integrating corneal topographic data and ocular wavefront data with primary ametropia measurements to create a soft contact lens design |
| DE19938203A1 (en) | 1999-08-11 | 2001-02-15 | Aesculap Meditec Gmbh | Method and device for correcting visual defects in the human eye |
| US6086204A (en) * | 1999-09-20 | 2000-07-11 | Magnante; Peter C. | Methods and devices to design and fabricate surfaces on contact lenses and on corneal tissue that correct the eye's optical aberrations |
| FR2798744B1 (en) | 1999-09-22 | 2002-04-05 | Essilor Int | METHOD FOR DETERMINING THE SHAPE OF AN OPHTHALMIC CONTACT LENS FOR CORRECTING OPTICAL ABERRATIONS OF THE EYE BEYOND DEFOCUSING OR ASTIGMATISM AND DEVICE FOR IMPLEMENTING THIS METHOD |
| US7233312B2 (en) * | 2000-07-31 | 2007-06-19 | Panaseca, Inc. | System and method for optimal viewing of computer monitors to minimize eyestrain |
| US6592223B1 (en) * | 1999-10-07 | 2003-07-15 | Panaseca, Inc. | System and method for optimal viewing of computer monitors to minimize eyestrain |
| CN1309340C (en) * | 1999-10-21 | 2007-04-11 | 泰克诺拉斯眼科系统有限公司 | Customized corneal profiling |
| DE60030995T2 (en) * | 1999-10-21 | 2007-06-06 | Technolas Gmbh Ophthalmologische Systeme | Iris recognition and tracking to treat visual irregularities of the eye |
| US6264328B1 (en) | 1999-10-21 | 2001-07-24 | University Of Rochester | Wavefront sensor with off-axis illumination |
| DE19950792A1 (en) * | 1999-10-21 | 2001-04-26 | Technolas Gmbh | Ophthalmic wavefront aberration diagnostic tool, has camera that aids in focusing aerial image from lenslet array, on wavefront sensor |
| ES2256054T3 (en) | 1999-10-21 | 2006-07-16 | Technolas Gmbh Ophthalmologische Systeme | APPARATUS FOR OPTALMIC REFRACTORY CORRECTION. |
| WO2001028477A1 (en) | 1999-10-21 | 2001-04-26 | Technolas Gmbh Ophthalmologische Systeme | Multi-step laser correction of ophthalmic refractive errors |
| US6199986B1 (en) * | 1999-10-21 | 2001-03-13 | University Of Rochester | Rapid, automatic measurement of the eye's wave aberration |
| DE19954523C2 (en) * | 1999-11-12 | 2002-01-31 | Johannes Junger | Process for surface treatment of a contact lens for individual adaptation to the eye system |
| EP1104663A3 (en) * | 1999-11-15 | 2005-01-19 | Kabushiki Kaisha Topcon | Eye aberration characteristic measuring apparatus |
| DE19958436B4 (en) * | 1999-12-03 | 2014-07-17 | Carl Zeiss Meditec Ag | Apparatus and method for active, physiologically evaluated, comprehensive correction of the aberrations of the human eye |
| US6563947B1 (en) | 1999-12-10 | 2003-05-13 | 20/10 Perfect Vision Optische Geraete Gmbh | Application specified integrated circuit for use in wavefront detection |
| CA2393435A1 (en) * | 1999-12-23 | 2001-07-05 | Fergal Patrick Shevlin | A display device |
| US6419671B1 (en) | 1999-12-23 | 2002-07-16 | Visx, Incorporated | Optical feedback system for vision correction |
| WO2001047449A1 (en) * | 1999-12-29 | 2001-07-05 | New England College Of Optometry | Myopia progression retardation by optical defect correction |
| DE10001131A1 (en) * | 2000-01-13 | 2001-07-19 | Wavelight Laser Technologie Ag | Device for ophthalmic eye treatment with fixation light beam |
| US6452145B1 (en) | 2000-01-27 | 2002-09-17 | Aoptix Technologies, Inc. | Method and apparatus for wavefront sensing |
| US6439720B1 (en) | 2000-01-27 | 2002-08-27 | Aoptics, Inc. | Method and apparatus for measuring optical aberrations of the human eye |
| US6874897B2 (en) * | 2000-01-27 | 2005-04-05 | Aoptix Technologies, Inc. | Deformable curvature mirror with unipolar-wiring |
| US6464364B2 (en) | 2000-01-27 | 2002-10-15 | Aoptix Technologies, Inc. | Deformable curvature mirror |
| US6695207B1 (en) | 2000-02-04 | 2004-02-24 | Carroll Boyd Norris, Jr. | System for secure, identity authenticated, and immediate financial transactions as well as activation of varied instrumentalities |
| US6550917B1 (en) * | 2000-02-11 | 2003-04-22 | Wavefront Sciences, Inc. | Dynamic range extension techniques for a wavefront sensor including use in ophthalmic measurement |
| US7455407B2 (en) * | 2000-02-11 | 2008-11-25 | Amo Wavefront Sciences, Llc | System and method of measuring and mapping three dimensional structures |
| DE10006896A1 (en) * | 2000-02-16 | 2001-08-30 | Wavelight Laser Technologie Ag | Production of an intraocular or optical contact lens a blank is produced mechanically and the surface profile material is removed by laser beams according to the calculated structure required to correct the vision |
| US6220707B1 (en) | 2000-02-25 | 2001-04-24 | 20/10 Perfect Vision Optische Geraete Gmbh | Method for programming an active mirror to mimic a wavefront |
| AUPQ591800A0 (en) * | 2000-02-25 | 2000-03-23 | Sola International Holdings Ltd | System for prescribing and/or dispensing ophthalmic lenses |
| US6234631B1 (en) * | 2000-03-09 | 2001-05-22 | Lasersight Technologies, Inc. | Combination advanced corneal topography/wave front aberration measurement |
| US6394999B1 (en) * | 2000-03-13 | 2002-05-28 | Memphis Eye & Cataract Associates Ambulatory Surgery Center | Laser eye surgery system using wavefront sensor analysis to control digital micromirror device (DMD) mirror patterns |
| US6923802B2 (en) * | 2000-03-13 | 2005-08-02 | Memphis Eye & Cataract Assoc. | System for generating ablation profiles for laser refractive eye surgery |
| EP1658829A1 (en) * | 2000-03-20 | 2006-05-24 | California Institute of Technology | Application of wavefront sensor to lenses capable of post-fabrication power modification |
| EP2042125A3 (en) * | 2000-03-20 | 2009-04-15 | California Institute of Technology | Application of wavefront sensor to lenses capable of post-fabrication power modification |
| ATE268150T1 (en) | 2000-03-22 | 2004-06-15 | Alcon Inc | OPTIMIZATION OF ABLATION CORRECTION OF AN OPTICAL SYSTEM |
| US7044944B2 (en) * | 2000-03-22 | 2006-05-16 | Alcon Refractivehorizons, Inc. | Optimization of ablation correction of an optical system and associated methods |
| ES2163373B1 (en) * | 2000-03-24 | 2003-04-16 | Univ Catalunya Politecnica | DEVICE OF OBJECTIVE MEASURE OF IMPROVEMENT IN THE OPTICAL QUALITY OF THE EYE. |
| US6659613B2 (en) * | 2000-03-27 | 2003-12-09 | Board Of Regents, The University Of Texas System | Methods and systems for measuring local scattering and aberration properties of optical media |
| WO2001078585A2 (en) | 2000-04-19 | 2001-10-25 | Alcon Universal Ltd. | Wavefront sensor for objective measurement of an optical system and associated methods |
| WO2001082228A2 (en) * | 2000-04-25 | 2001-11-01 | Alcon Universal Ltd. | Spatial filter for enhancing hartmann-shack images and associated methods |
| US6413276B1 (en) | 2000-04-26 | 2002-07-02 | Emmetropia, Inc. | Modified intraocular lens and method of correcting optical aberrations therein |
| US6338559B1 (en) * | 2000-04-28 | 2002-01-15 | University Of Rochester | Apparatus and method for improving vision and retinal imaging |
| US6460997B1 (en) | 2000-05-08 | 2002-10-08 | Alcon Universal Ltd. | Apparatus and method for objective measurements of optical systems using wavefront analysis |
| AU5747801A (en) * | 2000-05-09 | 2001-11-20 | Memphis Eye And Cataract Assoc | Method and system for control of high resolution high speed digital micromirror device for laser refractive eye surgery |
| JP4517211B2 (en) * | 2000-05-12 | 2010-08-04 | 株式会社トプコン | Eye characteristic measuring device |
| US6382795B1 (en) | 2000-05-20 | 2002-05-07 | Carl Zeiss, Inc. | Method and apparatus for measuring refractive errors of an eye |
| US6382793B1 (en) | 2000-05-20 | 2002-05-07 | Carl Zeiss, Inc. | Method and apparatus for measuring a wavefront |
| ATE381303T1 (en) * | 2000-05-23 | 2008-01-15 | Amo Groningen Bv | METHOD FOR PRODUCING OPHTALMIC LENSES WITH REDUCED ABBERRATIONS |
| US6609793B2 (en) * | 2000-05-23 | 2003-08-26 | Pharmacia Groningen Bv | Methods of obtaining ophthalmic lenses providing the eye with reduced aberrations |
| US8020995B2 (en) * | 2001-05-23 | 2011-09-20 | Amo Groningen Bv | Methods of obtaining ophthalmic lenses providing the eye with reduced aberrations |
| US6685317B2 (en) | 2000-06-13 | 2004-02-03 | Massie Research Laboratories, Inc. | Digital eye camera |
| US6544286B1 (en) * | 2000-07-18 | 2003-04-08 | Tissue Engineering Refraction, Inc. | Pre-fabricated corneal tissue lens method of corneal overlay to correct vision |
| IL137635A0 (en) * | 2000-08-01 | 2001-10-31 | Visionix Ltd | Apparatus for interactive optometry |
| US6566627B2 (en) * | 2000-08-11 | 2003-05-20 | Westar Photonics, Inc. | Laser method for shaping of optical lenses |
| US6830712B1 (en) * | 2000-08-28 | 2004-12-14 | Johnson & Johnson Vision Care, Inc. | Deformable molds and methods for their use in the manufacture of ophthalmic lenses |
| US6499843B1 (en) | 2000-09-13 | 2002-12-31 | Bausch & Lomb Incorporated | Customized vision correction method and business |
| US6536898B1 (en) * | 2000-09-15 | 2003-03-25 | The Regents Of The University Of Colorado | Extended depth of field optics for human vision |
| US6486943B1 (en) * | 2000-09-19 | 2002-11-26 | The Schepens Eye Research Institute, Inc. | Methods and apparatus for measurement and correction of optical aberration |
| US6406146B1 (en) | 2000-09-21 | 2002-06-18 | Carl Zeiss, Inc. | Wavefront refractor simultaneously recording two hartmann-shack images |
| MXPA03002436A (en) * | 2000-09-21 | 2003-08-19 | Visx Inc | Enhanced wavefront ablation system. |
| EP1322215B1 (en) * | 2000-09-26 | 2008-04-16 | Calhoun Vision Inc. | Power adjustment of adjustable lens |
| AU2001294818B2 (en) * | 2000-09-26 | 2006-08-17 | Calhoun Vision, Inc. | Power adjustment of adjustable lens |
| JP3860405B2 (en) * | 2000-09-29 | 2006-12-20 | 株式会社ニデック | Cornea surgery device |
| US6616279B1 (en) * | 2000-10-02 | 2003-09-09 | Johnson & Johnson Vision Care, Inc. | Method and apparatus for measuring wavefront aberrations |
| CA2425256A1 (en) * | 2000-10-10 | 2002-04-18 | David R. Williams | Determination of ocular refraction from wavefront aberration data |
| JP2004511786A (en) | 2000-10-11 | 2004-04-15 | カルホーン ビジョン インコーポレーテッド | Optical tunable aberration conjugator |
| US6382797B1 (en) * | 2000-10-17 | 2002-05-07 | 20/10 Perfect Vision Optische Geraete Gmbh | Aberration-free delivery system |
| US6428533B1 (en) * | 2000-10-17 | 2002-08-06 | 20/10 Perfect Vision Optische Geraete Gmbh | Closed loop control for refractive laser surgery (LASIK) |
| US6554425B1 (en) | 2000-10-17 | 2003-04-29 | Johnson & Johnson Vision Care, Inc. | Ophthalmic lenses for high order aberration correction and processes for production of the lenses |
| AU2002213370A1 (en) | 2000-10-20 | 2002-05-06 | Wavefront Sciences Inc. | Method for computing visual performance from objective ocular aberration measurements |
| US6827444B2 (en) | 2000-10-20 | 2004-12-07 | University Of Rochester | Rapid, automatic measurement of the eye's wave aberration |
| WO2002034178A1 (en) * | 2000-10-20 | 2002-05-02 | Bausch & Lomb Incorporated | Method and system for improving vision |
| US6464357B1 (en) * | 2000-10-20 | 2002-10-15 | Kestrel Corporation | Wavefront characterization of corneas |
| US6695880B1 (en) | 2000-10-24 | 2004-02-24 | Johnson & Johnson Vision Care, Inc. | Intraocular lenses and methods for their manufacture |
| AU2001295056A1 (en) | 2000-10-30 | 2002-05-15 | Johnson And Johnson Vision Care, Inc. | Wavefront measurement |
| US6595639B1 (en) | 2000-11-10 | 2003-07-22 | Ocular Sciences, Inc. | Junctionless ophthalmic lenses and methods for making same |
| US7152975B2 (en) * | 2000-11-10 | 2006-12-26 | Cooper Vision, Inc. | Junctionless ophthalmic lenses and methods for making same |
| US7293871B2 (en) * | 2000-11-27 | 2007-11-13 | Ophthonix, Inc. | Apparatus and method of correcting higher-order aberrations of the human eye |
| US6813082B2 (en) | 2000-11-27 | 2004-11-02 | Ophthonix, Inc. | Wavefront aberrator and method of manufacturing |
| US6563572B1 (en) * | 2000-12-07 | 2003-05-13 | The United States Of America As Represented By The Secretary Of The Air Force | Correlating shack-hartmann wavefront sensor |
| US20020071095A1 (en) * | 2000-12-08 | 2002-06-13 | Roffman Jefrey H. | Composite surface contact lenses |
| US6547391B2 (en) * | 2000-12-08 | 2003-04-15 | Johnson & Johnson Vision Care, Inc. | Ocular aberration correction taking into account fluctuations due to biophysical rhythms |
| MXPA03005113A (en) | 2000-12-08 | 2004-01-29 | Visx Inc | Direct wavefront-based corneal ablation treatment program. |
| SE0004829D0 (en) * | 2000-12-22 | 2000-12-22 | Pharmacia Groningen Bv | Methods of obtaining ophthalmic lenses providing the eye with reduced aberrations |
| JP3797874B2 (en) * | 2000-12-26 | 2006-07-19 | オリンパス株式会社 | Scanning optical microscope |
| US6757310B2 (en) | 2001-01-17 | 2004-06-29 | Ming Lai | Solid-state laser for customized cornea ablation |
| BR0206542A (en) | 2001-01-17 | 2004-06-22 | E Vision Llc | System and method employing an electroactive lens with integrated components |
| US6736507B2 (en) | 2001-01-22 | 2004-05-18 | Alexis Kudryashov | High resolution, multispectral, wide field of view retinal imager |
| US6331059B1 (en) | 2001-01-22 | 2001-12-18 | Kestrel Corporation | High resolution, multispectral, wide field of view retinal imager |
| US7422714B1 (en) | 2001-01-24 | 2008-09-09 | Cornerstone Research Group, Inc. | Method of using a shape memory material as a mandrel for composite part manufacturing |
| DE10103763C2 (en) * | 2001-01-27 | 2003-04-03 | Zeiss Carl Meditec Ag | Method and device for the subjective determination of aberrations of higher order |
| US6361170B1 (en) * | 2001-02-14 | 2002-03-26 | Heidelberg Engineering Optische Messysteme Gmbh | Aberration-free imaging of the fundus of the human eye |
| WO2002075367A2 (en) * | 2001-03-15 | 2002-09-26 | Wavefront Sciences, Inc. | Tomographic wavefront analysis system |
| SE0101293D0 (en) * | 2001-04-11 | 2001-04-11 | Pharmacia Groningen Bv | Technical field of the invention |
| SG154324A1 (en) | 2001-04-18 | 2009-08-28 | Bausch & Lomb | Objective manifest refraction |
| US6746121B2 (en) * | 2001-04-27 | 2004-06-08 | Denwood F. Ross | Defocus and astigmatism compensation in a wavefront aberration measurement system |
| DE01274188T1 (en) * | 2001-04-27 | 2004-07-15 | Bausch & Lomb Inc. | IRIS PATTERN RECOGNITION AND ORIENTATION |
| EP1390802A1 (en) | 2001-04-27 | 2004-02-25 | Novartis AG | Automatic lens design and manufacturing system |
| US6598974B2 (en) * | 2001-05-08 | 2003-07-29 | Johnson & Johnson Vision Care, Inc. | Method and apparatus for measuring wavefront aberrations |
| US6561648B2 (en) * | 2001-05-23 | 2003-05-13 | David E. Thomas | System and method for reconstruction of aberrated wavefronts |
| US6394605B1 (en) | 2001-05-23 | 2002-05-28 | Alcon Universal Ltd. | Fogging method for a wavefront sensor |
| IL143503A0 (en) | 2001-05-31 | 2002-04-21 | Visionix Ltd | Aberration correction spectacle lens |
| US7217375B2 (en) * | 2001-06-04 | 2007-05-15 | Ophthonix, Inc. | Apparatus and method of fabricating a compensating element for wavefront correction using spatially localized curing of resin mixtures |
| US6609794B2 (en) | 2001-06-05 | 2003-08-26 | Adaptive Optics Associates, Inc. | Method of treating the human eye with a wavefront sensor-based ophthalmic instrument |
| US6721510B2 (en) | 2001-06-26 | 2004-04-13 | Aoptix Technologies, Inc. | Atmospheric optical data transmission system |
| FR2828396B1 (en) * | 2001-08-12 | 2004-05-07 | Samuel Henri Bucourt | DEVICE FOR MEASURING ABERRATIONS OF AN EYE-LIKE SYSTEM |
| JP4157839B2 (en) * | 2001-08-30 | 2008-10-01 | ユニバーシティー オブ ロチェスター | Retinal region imaging method and system for living eye |
| US6631991B2 (en) | 2001-08-31 | 2003-10-14 | Adaptive Optics Associates, Inc. | Ophthalmic instrument having hartmann wavefront sensor deriving location of spots with spot fitting techniques |
| US6827442B2 (en) * | 2001-09-12 | 2004-12-07 | Denwood F. Ross | Ophthalmic wavefront measuring devices |
| US6575572B2 (en) | 2001-09-21 | 2003-06-10 | Carl Zeiss Ophthalmic Systems, Inc. | Method and apparatus for measuring optical aberrations of an eye |
| JP2005505789A (en) * | 2001-10-05 | 2005-02-24 | イー・ビジョン・エルエルシー | Hybrid electroactive lens |
| US6554429B1 (en) | 2001-10-15 | 2003-04-29 | Alcon, Inc. | Method for determining accommodation |
| EP1902672B1 (en) | 2001-10-19 | 2010-04-28 | Bausch & Lomb Incorporated | Presbyopic vision improvement |
| ES2316614T3 (en) * | 2001-10-19 | 2009-04-16 | BAUSCH & LOMB INCORPORATED | IMPROVEMENTS OF THE CORRECTION OF THE VISION WITH PRESBICIA. |
| AU2008201900B2 (en) * | 2001-10-25 | 2011-11-24 | Essilor International (Compagnie Generale D'optique) | Eyeglass having variable index layer |
| US6688745B2 (en) | 2001-10-25 | 2004-02-10 | Johnson & Johnson Vision Care, Inc. | Subjective refinement of wavefront measurements |
| US6712466B2 (en) | 2001-10-25 | 2004-03-30 | Ophthonix, Inc. | Eyeglass manufacturing method using variable index layer |
| US6682195B2 (en) * | 2001-10-25 | 2004-01-27 | Ophthonix, Inc. | Custom eyeglass manufacturing method |
| US7434931B2 (en) | 2001-10-25 | 2008-10-14 | Ophthonix | Custom eyeglass manufacturing method |
| US7377647B2 (en) * | 2001-11-13 | 2008-05-27 | Philadelphia Retina Endowment Fund | Clarifying an image of an object to perform a procedure on the object |
| US7775665B2 (en) * | 2001-11-13 | 2010-08-17 | Dellavecchia Michael A | Method for optically scanning objects |
| US6648473B2 (en) | 2001-11-13 | 2003-11-18 | Philadelphia Retina Endowment Fund | High-resolution retina imaging and eye aberration diagnostics using stochastic parallel perturbation gradient descent optimization adaptive optics |
| US20040165147A1 (en) * | 2001-11-13 | 2004-08-26 | Della Vecchia Michael A. | Determining iris biometric and spatial orientation of an iris in accordance with same |
| US7226166B2 (en) * | 2001-11-13 | 2007-06-05 | Philadelphia Retina Endowment Fund | Optimizing the properties of electromagnetic energy in a medium using stochastic parallel perturbation gradient descent optimization adaptive optics |
| US6781681B2 (en) | 2001-12-10 | 2004-08-24 | Ophthonix, Inc. | System and method for wavefront measurement |
| US7034949B2 (en) * | 2001-12-10 | 2006-04-25 | Ophthonix, Inc. | Systems and methods for wavefront measurement |
| US6739721B2 (en) | 2001-12-11 | 2004-05-25 | Bausch And Lomb, Inc | Method and apparatus for calibrating and certifying accuracy of a wavefront sensing device |
| US20030107814A1 (en) * | 2001-12-11 | 2003-06-12 | Altmann Griffith E. | Method and apparatus for improving the dynamic range and accuracy of a Shack-Hartmann wavefront sensor |
| US6755524B2 (en) * | 2001-12-12 | 2004-06-29 | Inray Ltd. | Ophthalmic optical elements and methods for the design thereof |
| US6637884B2 (en) | 2001-12-14 | 2003-10-28 | Bausch & Lomb Incorporated | Aberrometer calibration |
| US6736509B2 (en) | 2001-12-21 | 2004-05-18 | Bausch And Lomb, Inc. | Aberrometer illumination apparatus and method |
| EP1474084A4 (en) | 2002-01-17 | 2007-04-18 | Edward Perez | Methods for producing epithelial flaps on the cornea and for placement of ocular devices and lenses beneath an epithelial flap or membrane, epithelial delaminating devices, and structures of epithelium and ocular devices and lenses |
| US20030142271A1 (en) | 2002-01-30 | 2003-07-31 | Ross Denwood F. | Aberration and corneal topography measurement |
| US7115305B2 (en) | 2002-02-01 | 2006-10-03 | California Institute Of Technology | Method of producing regular arrays of nano-scale objects using nano-structured block-copolymeric materials |
| CA2475389C (en) * | 2002-02-11 | 2009-07-14 | Visx, Inc. | Closed loop system and method for ablating lenses with aberrations |
| WO2003068051A2 (en) * | 2002-02-12 | 2003-08-21 | Visx, Inc. | Flexible scanning beam imaging system |
| US20050174535A1 (en) * | 2003-02-13 | 2005-08-11 | Lai Shui T. | Apparatus and method for determining subjective responses using objective characterization of vision based on wavefront sensing |
| US6761454B2 (en) | 2002-02-13 | 2004-07-13 | Ophthonix, Inc. | Apparatus and method for determining objective refraction using wavefront sensing |
| JP3916482B2 (en) * | 2002-02-27 | 2007-05-16 | 株式会社ニデック | Ophthalmic equipment |
| US20080106633A1 (en) * | 2002-03-13 | 2008-05-08 | Blum Ronald D | Electro-optic lens with integrated components for varying refractive properties |
| US7130835B2 (en) | 2002-03-28 | 2006-10-31 | Bausch & Lomb Incorporated | System and method for predictive ophthalmic correction |
| WO2003092485A1 (en) | 2002-05-03 | 2003-11-13 | University Of Rochester | Sharpness metric for vision quality |
| US6663240B2 (en) | 2002-05-15 | 2003-12-16 | Alcon, Inc. | Method of manufacturing customized intraocular lenses |
| AU2002346438A1 (en) * | 2002-05-30 | 2003-12-19 | Visx, Inc. | Torsional eye orientation and position |
| EP1513477A1 (en) | 2002-05-31 | 2005-03-16 | Carl Zeiss Meditec AG | Method for controlling a device for treating the human eye |
| US7364296B2 (en) * | 2002-06-12 | 2008-04-29 | University Of Rochester | Method and apparatus for improving both lateral and axial resolution in ophthalmoscopy |
| US7083609B2 (en) | 2002-06-13 | 2006-08-01 | Visx, Incorporated | Corneal topography-based target warping |
| DE10227120A1 (en) * | 2002-06-15 | 2004-03-04 | Carl Zeiss Jena Gmbh | Microscope, in particular laser scanning microscope with adaptive optical device |
| US20040021826A1 (en) * | 2002-08-01 | 2004-02-05 | Sarver Edwin J. | Combination advanced corneal topography/wave front aberration measurement |
| EP1546984A1 (en) * | 2002-09-06 | 2005-06-29 | Quarter Lambda Technologies Inc. | Hybrid contact lens system and method |
| US7104648B2 (en) * | 2002-09-06 | 2006-09-12 | Synergeyes, Inc. | Hybrid contact lens system and method |
| US7163292B2 (en) * | 2002-09-06 | 2007-01-16 | Synergeyes, Inc. | Hybrid contact lens system and method |
| US7322694B2 (en) * | 2002-09-06 | 2008-01-29 | Synergeyes, Inc. | Hybrid contact lens system and method |
| EP1543767A4 (en) | 2002-09-26 | 2008-03-19 | Topcon Corp | Eye characteristics measuring system |
| DE10245081A1 (en) * | 2002-09-27 | 2004-04-01 | Carl Zeiss | Process for processing a prefabricated or semi-finished product |
| CA2501217C (en) * | 2002-10-04 | 2013-01-08 | Carl Zeiss Ag | Method for producing a lens, and a lens produced thereby |
| US7195354B2 (en) * | 2002-10-04 | 2007-03-27 | The Regents Of The University Of California | Adaptive ophthalmologic system |
| US6798560B2 (en) * | 2002-10-11 | 2004-09-28 | Exajoula, Llc | Micromirror systems with open support structures |
| US6825968B2 (en) * | 2002-10-11 | 2004-11-30 | Exajoule, Llc | Micromirror systems with electrodes configured for sequential mirror attraction |
| US6870659B2 (en) * | 2002-10-11 | 2005-03-22 | Exajoule, Llc | Micromirror systems with side-supported mirrors and concealed flexure members |
| US7406263B2 (en) * | 2002-10-17 | 2008-07-29 | Aoptix Technologies | Combined wavefront sensor and data detector for a free space optical communications system with adaptive optics |
| US7381221B2 (en) * | 2002-11-08 | 2008-06-03 | Advanced Medical Optics, Inc. | Multi-zonal monofocal intraocular lens for correcting optical aberrations |
| US7232436B2 (en) * | 2002-11-13 | 2007-06-19 | Josef Bille | Closed loop control for intrastromal wavefront-guided ablation with fractionated treatment program |
| US6887232B2 (en) * | 2002-11-13 | 2005-05-03 | 20/10 Perfect Vision Optische Geraete Gmbh | Closed loop control for intrastromal wavefront-guided ablation |
| US7209414B2 (en) * | 2002-11-15 | 2007-04-24 | Plasmon Lms, Inc | Spherical aberration compensation by wavelength |
| ITTO20021007A1 (en) * | 2002-11-19 | 2004-05-20 | Franco Bartoli | EXCIMER LASER EQUIPMENT AND DRIVING METHOD |
| AU2002953061A0 (en) * | 2002-11-20 | 2002-12-19 | Sola International Holdings Ltd | Method for designing progressive lenses |
| US7407285B2 (en) | 2002-11-20 | 2008-08-05 | Ming Lai | Method and apparatus for obtaining patient-verified prescription of high order aberrations |
| US7896916B2 (en) * | 2002-11-29 | 2011-03-01 | Amo Groningen B.V. | Multifocal ophthalmic lens |
| SE0203564D0 (en) | 2002-11-29 | 2002-11-29 | Pharmacia Groningen Bv | Multifocal opthalmic lens |
| US7434936B2 (en) * | 2002-12-06 | 2008-10-14 | Amo Manufacturing Usa, Llc | Residual accommodation threshold for correction of presbyopia and other presbyopia correction using patient data |
| US8911086B2 (en) | 2002-12-06 | 2014-12-16 | Amo Manufacturing Usa, Llc | Compound modulation transfer function for laser surgery and other optical applications |
| US8342686B2 (en) | 2002-12-06 | 2013-01-01 | Amo Manufacturing Usa, Llc. | Compound modulation transfer function for laser surgery and other optical applications |
| US7320517B2 (en) | 2002-12-06 | 2008-01-22 | Visx, Incorporated | Compound modulation transfer function for laser surgery and other optical applications |
| EP1567907A4 (en) * | 2002-12-06 | 2009-09-02 | Amo Mfg Usa Llc | Presbyopia correction using patient data |
| US7338165B2 (en) * | 2003-06-20 | 2008-03-04 | Visx, Incorporated | Systems and methods for prediction of objective visual acuity based on wavefront measurements |
| US6939342B2 (en) * | 2002-12-12 | 2005-09-06 | Bausch And Lomb Incorporated | System and method for evaluating a secondary LASIK treatment |
| US7289736B1 (en) | 2003-01-13 | 2007-10-30 | Aoptix Technologies | Adaptive optics imaging system with object acquisition capability |
| US7286766B2 (en) | 2003-01-16 | 2007-10-23 | Aoptix Technologies, Inc. | Free space optical communication system with power level management |
| US7036931B2 (en) * | 2003-01-29 | 2006-05-02 | Novartis Ag | Ophthalmic lenses |
| US6736510B1 (en) | 2003-02-04 | 2004-05-18 | Ware Tec Vision Systems, Inc. | Ophthalmic talbot-moire wavefront sensor |
| DE10306087B4 (en) | 2003-02-07 | 2022-07-14 | Carl Zeiss Meditec Ag | Microscope, method for increasing the image quality of a microscope and mirror element for a microscope |
| US6910770B2 (en) * | 2003-02-10 | 2005-06-28 | Visx, Incorporated | Eye refractor with active mirror wavefront sensor |
| US20040227932A1 (en) * | 2003-02-13 | 2004-11-18 | Geunyoung Yoon | Large dynamic range shack-hartmann wavefront sensor |
| US7414712B2 (en) | 2003-02-13 | 2008-08-19 | University Of Rochester | Large dynamic range Shack-Hartmann wavefront sensor |
| US6900922B2 (en) * | 2003-02-24 | 2005-05-31 | Exajoule, Llc | Multi-tilt micromirror systems with concealed hinge structures |
| US6906848B2 (en) * | 2003-02-24 | 2005-06-14 | Exajoule, Llc | Micromirror systems with concealed multi-piece hinge structures |
| US6988801B2 (en) * | 2003-03-25 | 2006-01-24 | University Of Rochester | Compact portable wavefront sensor |
| WO2004086952A2 (en) | 2003-03-28 | 2004-10-14 | Digital Vision, Llc | Application of neuro-ocular wavefront data in vision correction |
| US7556378B1 (en) | 2003-04-10 | 2009-07-07 | Tsontcho Ianchulev | Intraoperative estimation of intraocular lens power |
| MXPA05011131A (en) * | 2003-04-18 | 2006-03-10 | Visx Inc | Systems and methods for correcting high order aberrations in laser refractive surgery. |
| WO2004096014A2 (en) * | 2003-04-28 | 2004-11-11 | University Of Rochester | Metrics to predict subjective impact of eye's wave aberration |
| US7387394B2 (en) | 2003-04-30 | 2008-06-17 | Topcon Corporation | Deformable mirror control device and device for observing retina of eye |
| JP4121890B2 (en) | 2003-04-30 | 2008-07-23 | 株式会社トプコン | Fundus observation apparatus and fundus observation method |
| US7057806B2 (en) * | 2003-05-09 | 2006-06-06 | 3M Innovative Properties Company | Scanning laser microscope with wavefront sensor |
| US20040263779A1 (en) * | 2003-06-12 | 2004-12-30 | Visx, Inc. | Hartmann-Shack wavefront measurement |
| US7458683B2 (en) * | 2003-06-16 | 2008-12-02 | Amo Manufacturing Usa, Llc | Methods and devices for registering optical measurement datasets of an optical system |
| US8596787B2 (en) | 2003-06-20 | 2013-12-03 | Amo Manufacturing Usa, Llc | Systems and methods for prediction of objective visual acuity based on wavefront measurements |
| US7175278B2 (en) * | 2003-06-20 | 2007-02-13 | Visx, Inc. | Wavefront reconstruction using fourier transformation and direct integration |
| US7168807B2 (en) * | 2003-06-20 | 2007-01-30 | Visx, Incorporated | Iterative fourier reconstruction for laser surgery and other optical applications |
| DE10333558A1 (en) * | 2003-07-23 | 2005-03-17 | Technovision Gmbh | Corneal keratoscopy based on a corneal wavefront measurement |
| DE10333794A1 (en) * | 2003-07-24 | 2005-03-03 | Technovision Gmbh | Method and device for online contact lens evaluation |
| DE10333813A1 (en) * | 2003-07-24 | 2005-02-17 | Technovision GmbH Gesellschaft für die Entwicklung medizinischer Technologie | Online wavefront measurement and display |
| JP4330400B2 (en) * | 2003-08-04 | 2009-09-16 | 株式会社ニデック | Ophthalmic equipment |
| BRPI0413590A (en) * | 2003-08-15 | 2006-10-17 | E Vision Llc | improved electroactive lens system |
| DE10348854A1 (en) * | 2003-10-20 | 2005-05-19 | Lar Ip Ventures Inc. | Method and device for determining the residual defective vision of a patient |
| US7226443B1 (en) | 2003-11-07 | 2007-06-05 | Alcon Refractivehorizons, Inc. | Optimization of ablation correction of an optical system and associated methods |
| US7284862B1 (en) | 2003-11-13 | 2007-10-23 | Md Lasers & Instruments, Inc. | Ophthalmic adaptive-optics device with a fast eye tracker and a slow deformable mirror |
| US7018039B2 (en) * | 2003-11-14 | 2006-03-28 | Synergeyes,Inc. | Contact lens |
| US20080269731A1 (en) * | 2003-11-19 | 2008-10-30 | Casimir Andrew Swinger | Method and apparatus applying patient-verified prescription of high order aberrations |
| US20050122473A1 (en) * | 2003-11-24 | 2005-06-09 | Curatu Eugene O. | Method and apparatus for aberroscope calibration and discrete compensation |
| WO2005057252A2 (en) * | 2003-12-02 | 2005-06-23 | Wavetec Vision Systems, Inc. | Interactive refractor incorporating wavefront sensing and adaptive optics |
| US7070276B2 (en) * | 2003-12-04 | 2006-07-04 | Rensselaer Polytechnic Institute | Apparatus and method for accommodative stimulation of an eye and simultaneous ipsilateral accommodative imaging |
| PL1699345T3 (en) * | 2003-12-12 | 2013-10-31 | Univ Indiana Res & Tech Corp | System and method for optimizing clinical optic prescriptions |
| DE10360570B4 (en) * | 2003-12-22 | 2006-01-12 | Carl Zeiss | Optical measuring system and optical measuring method |
| FR2865371B1 (en) * | 2004-01-22 | 2007-12-21 | Centre Nat Rech Scient | DEVICE AND METHOD FOR EXAMINING THE EYE, SYSTEM FOR EXAMINING THE EYE BY IN VIVO TOMOGRAPHY EQUIPPED WITH SAID DEVICE |
| FR2865370B1 (en) * | 2004-01-22 | 2006-04-28 | Centre Nat Rech Scient | SYSTEM AND METHOD FOR IN VIVO TOMOGRAPHY WITH HIGH LATERAL AND AXIAL RESOLUTION OF THE HUMAN RETINA |
| WO2005073689A1 (en) * | 2004-02-02 | 2005-08-11 | Iatia Imaging Pty Ltd | Apparatus and method for correcting for aberrations in a lens system |
| US7343099B2 (en) * | 2004-02-12 | 2008-03-11 | Metrologic Instruments, Inc. | Free space optical (FSO) laser communication system employing fade mitigation measures based on laser beam speckle tracking and locking principles |
| US7481536B2 (en) | 2004-02-19 | 2009-01-27 | Amo Manufacturing Usa, Llc | Methods and systems for differentiating left and right eye images |
| KR100900173B1 (en) * | 2004-02-20 | 2009-06-02 | 도오꾜오까고오교 가부시끼가이샤 | Base material for pattern forming material, positive resist composition and method of resist pattern formation |
| US7296893B2 (en) | 2004-03-03 | 2007-11-20 | Visx, Incorporated | Transformation methods of wavefront maps from one vertex distance to another |
| US20050241653A1 (en) | 2004-04-20 | 2005-11-03 | Wavetec Vision Systems, Inc. | Integrated surgical microscope and wavefront sensor |
| US20050237485A1 (en) * | 2004-04-21 | 2005-10-27 | Blum Ronald D | Method and apparatus for correcting vision |
| CN100430031C (en) * | 2004-04-26 | 2008-11-05 | 中国科学院光电技术研究所 | Binocular stereoscopic high-order aberration correction vision simulation system |
| JP2007536101A (en) | 2004-05-05 | 2007-12-13 | カリフォルニア インスティテュート オブ テクノロジー | Nanofiber array capillary lithography |
| US20050260388A1 (en) * | 2004-05-21 | 2005-11-24 | Lai Shui T | Apparatus and method of fabricating an ophthalmic lens for wavefront correction using spatially localized curing of photo-polymerization materials |
| US7387387B2 (en) * | 2004-06-17 | 2008-06-17 | Amo Manufacturing Usa, Llc | Correction of presbyopia using adaptive optics and associated methods |
| JP4510534B2 (en) * | 2004-06-22 | 2010-07-28 | 株式会社トプコン | Optical characteristic measuring device and fundus image observation device |
| US7708402B2 (en) * | 2004-06-25 | 2010-05-04 | Technion Research And Development Foundation Ltd. | Goggles for improved ocular vision |
| US7465299B2 (en) * | 2004-07-14 | 2008-12-16 | Luigi Rovati | Monitoring of retinal temperature during laser therapy |
| JP3946715B2 (en) * | 2004-07-28 | 2007-07-18 | 東京応化工業株式会社 | Positive resist composition and resist pattern forming method |
| JP4609838B2 (en) * | 2004-08-10 | 2011-01-12 | 株式会社ニデック | Cornea surgery device |
| US7377643B1 (en) * | 2004-08-13 | 2008-05-27 | Q Step Technologies, Inc. | Method and apparatus for eye imaging with position registration and constant pupil size |
| US7360893B2 (en) * | 2004-08-31 | 2008-04-22 | 20/10 Perfect Vision Optische Geraete Gmbh | Systems and methods for shaping wavefronts in polychromatic light using phase shifting elements |
| CN101065766A (en) * | 2004-09-03 | 2007-10-31 | 潘那西卡股份有限公司 | Vision center kiosk |
| JP4468119B2 (en) * | 2004-09-08 | 2010-05-26 | 東京応化工業株式会社 | Resist composition and resist pattern forming method |
| US20060066808A1 (en) * | 2004-09-27 | 2006-03-30 | Blum Ronald D | Ophthalmic lenses incorporating a diffractive element |
| AU2005319678B2 (en) * | 2004-10-25 | 2011-06-30 | Johnson & Johnson Surgical Vision, Inc. | Ophthalmic lens with multiple phase plates |
| US7922326B2 (en) | 2005-10-25 | 2011-04-12 | Abbott Medical Optics Inc. | Ophthalmic lens with multiple phase plates |
| JP4837323B2 (en) * | 2004-10-29 | 2011-12-14 | 東京応化工業株式会社 | Resist composition, resist pattern forming method and compound |
| US8021967B2 (en) | 2004-11-01 | 2011-09-20 | California Institute Of Technology | Nanoscale wicking methods and devices |
| US8931896B2 (en) | 2004-11-02 | 2015-01-13 | E-Vision Smart Optics Inc. | Eyewear including a docking station |
| US9801709B2 (en) | 2004-11-02 | 2017-10-31 | E-Vision Smart Optics, Inc. | Electro-active intraocular lenses |
| JP5064229B2 (en) * | 2004-11-02 | 2012-10-31 | イー・ビジョン・エルエルシー | Compound lens |
| US8778022B2 (en) | 2004-11-02 | 2014-07-15 | E-Vision Smart Optics Inc. | Electro-active intraocular lenses |
| SE0402769D0 (en) | 2004-11-12 | 2004-11-12 | Amo Groningen Bv | Method of selecting intraocular lenses |
| US7931373B2 (en) | 2004-12-03 | 2011-04-26 | The Invention Science Fund I, Llc | Vision modification with reflected image |
| US7334894B2 (en) * | 2004-12-03 | 2008-02-26 | Searete, Llc | Temporal vision modification |
| US7486988B2 (en) | 2004-12-03 | 2009-02-03 | Searete Llc | Method and system for adaptive vision modification |
| US7334892B2 (en) | 2004-12-03 | 2008-02-26 | Searete Llc | Method and system for vision enhancement |
| US7344244B2 (en) | 2004-12-03 | 2008-03-18 | Searete, Llc | Adjustable lens system with neural-based control |
| US7656569B2 (en) | 2004-12-03 | 2010-02-02 | Searete Llc | Vision modification with reflected image |
| US7390088B2 (en) | 2004-12-03 | 2008-06-24 | Searete Llc | Adjustable lens system with neural-based control |
| US7594727B2 (en) | 2004-12-03 | 2009-09-29 | Searete Llc | Vision modification with reflected image |
| US7350919B2 (en) | 2004-12-03 | 2008-04-01 | Searete Llc | Vision modification with reflected image |
| US8104892B2 (en) | 2004-12-03 | 2012-01-31 | The Invention Science Fund I, Llc | Vision modification with reflected image |
| US8244342B2 (en) | 2004-12-03 | 2012-08-14 | The Invention Science Fund I, Llc | Method and system for adaptive vision modification |
| US7470027B2 (en) | 2004-12-03 | 2008-12-30 | Searete Llc | Temporal vision modification |
| US9155483B2 (en) | 2004-12-03 | 2015-10-13 | The Invention Science Fund I, Llc | Vision modification with reflected image |
| US7869627B2 (en) * | 2004-12-07 | 2011-01-11 | Aoptix Technologies, Inc. | Post processing of iris images to increase image quality |
| US7418115B2 (en) | 2004-12-07 | 2008-08-26 | Aoptix Technologies, Inc. | Iris imaging using reflection from the eye |
| US7428320B2 (en) * | 2004-12-07 | 2008-09-23 | Aoptix Technologies, Inc. | Iris imaging using reflection from the eye |
| US20060126018A1 (en) * | 2004-12-10 | 2006-06-15 | Junzhong Liang | Methods and apparatus for wavefront sensing of human eyes |
| US20060126019A1 (en) * | 2004-12-10 | 2006-06-15 | Junzhong Liang | Methods and systems for wavefront analysis |
| US8597282B2 (en) | 2005-01-13 | 2013-12-03 | Amo Manufacturing Usa, Llc | Database system for centralized clinical and research applications with data from wavefront aberrometers |
| US8885139B2 (en) | 2005-01-21 | 2014-11-11 | Johnson & Johnson Vision Care | Adaptive electro-active lens with variable focal length |
| DE102005005932A1 (en) * | 2005-02-09 | 2006-08-17 | Carl Zeiss Meditec Ag | Focusing and astigmatism compensator for a fundus camera |
| US20060217691A1 (en) * | 2005-02-25 | 2006-09-28 | Georg Schuele | Real-time therapeutic dosimetry based on dynamic response of treated tissue |
| US8439502B2 (en) * | 2005-03-09 | 2013-05-14 | Advanced Vision Engineering, Inc | Algorithms and methods for determining aberration-induced vision symptoms in the eye from wave aberration |
| DE102005013558A1 (en) * | 2005-03-23 | 2006-09-28 | Carl Zeiss Meditec Ag | Method and device for increasing the depth of focus of an optical system |
| US7401922B2 (en) * | 2005-04-13 | 2008-07-22 | Synergeyes, Inc. | Method and apparatus for reducing or eliminating the progression of myopia |
| EP1871262B1 (en) * | 2005-04-14 | 2013-06-12 | University Of Rochester | System for treating vision refractive errors |
| US20060235513A1 (en) * | 2005-04-18 | 2006-10-19 | Price Francis W Jr | Corneal implants and methods of use |
| CN100449349C (en) * | 2005-04-20 | 2009-01-07 | 中国人民解放军国防科学技术大学 | Large aperture linear array Hartmann wavefront sensor |
| US7543936B2 (en) * | 2005-05-06 | 2009-06-09 | Synergeyes, Inc. | Hybrid contact lens system and method of fitting |
| US20060264917A1 (en) | 2005-05-20 | 2006-11-23 | Visx, Incorporated | Scleral lenses for custom optic evaluation and visual performance improvement |
| US7441901B2 (en) * | 2005-06-14 | 2008-10-28 | Advanced Vision Engineering, Inc. | Multitask vision architecture for refractive vision corrections |
| US7591556B2 (en) * | 2005-06-24 | 2009-09-22 | Boston Foundation For Sight | Scleral contact lens with grooves and method of making lens |
| US7261412B2 (en) | 2005-06-30 | 2007-08-28 | Visx, Incorporated | Presbyopia correction through negative high-order spherical aberration |
| US20070019159A1 (en) * | 2005-07-20 | 2007-01-25 | Michiko Nakanishi | Deforming method for deformable mirror, aberration compensation method for optical apparatus, aberration compensation method of ocular fundus observation apparatus, aberration compensation apparatus, optical apparatus and ocular funds observation apparatus |
| ATE480181T1 (en) * | 2005-08-18 | 2010-09-15 | Imagine Eyes | METHOD AND SYSTEM FOR CORRECTING DEVIATIONS OF THE EYE FOR AN OPHTHALMIC INSTRUMENT |
| GB2429522A (en) * | 2005-08-26 | 2007-02-28 | Univ Kent Canterbury | Optical mapping apparatus |
| US7331674B2 (en) * | 2005-09-02 | 2008-02-19 | Visx, Incorporated | Calculating Zernike coefficients from Fourier coefficients |
| DE102005046130A1 (en) * | 2005-09-27 | 2007-03-29 | Bausch & Lomb Inc. | Excimer laser-eye surgical system, has eye tracing device sending instruction signal to laser device via bidirectional bus to fire shot, when preset position data is same as initial position data of scanning device for shot |
| US7377637B2 (en) * | 2005-10-11 | 2008-05-27 | Synergeyes, Inc. | Hybrid contact lens system and method of fitting |
| US8801781B2 (en) * | 2005-10-26 | 2014-08-12 | Abbott Medical Optics Inc. | Intraocular lens for correcting corneal coma |
| WO2007055916A2 (en) * | 2005-11-07 | 2007-05-18 | The Rockefeller University | Reagents, methods and systems for selecting a cytotoxic antibody or variant thereof |
| DE102005053297A1 (en) * | 2005-11-08 | 2007-05-10 | Bausch & Lomb Inc. | System and method for correcting ophthalmic refractive errors |
| TWI262325B (en) * | 2005-11-16 | 2006-09-21 | Ind Tech Res Inst | Eye aberration measurement and calibrating equipment and its method |
| DE102005054691A1 (en) * | 2005-11-16 | 2007-05-24 | Bausch & Lomb Inc. | Method and device for determining the visual acuity of an eye |
| WO2007073848A2 (en) | 2005-12-15 | 2007-07-05 | Franz Fankhauser | Device measuring eyes with the aid of dynamic light scattering |
| WO2007071401A1 (en) * | 2005-12-21 | 2007-06-28 | Novartis Ag | Adaptive optic ophthalmic design system |
| US20070159562A1 (en) * | 2006-01-10 | 2007-07-12 | Haddock Joshua N | Device and method for manufacturing an electro-active spectacle lens involving a mechanically flexible integration insert |
| US7520609B2 (en) * | 2006-01-18 | 2009-04-21 | Amo Manufacturing Llc | Non-invasive measurement of tear volume systems and methods |
| US8820929B2 (en) | 2006-01-20 | 2014-09-02 | Clarity Medical Systems, Inc. | Real-time measurement/display/record/playback of wavefront data for use in vision correction procedures |
| US8100530B2 (en) | 2006-01-20 | 2012-01-24 | Clarity Medical Systems, Inc. | Optimizing vision correction procedures |
| US9113819B2 (en) | 2006-01-20 | 2015-08-25 | Clarity Medical Systems, Inc. | Apparatus and method for operating a real time large diopter range sequential wavefront sensor |
| US8777413B2 (en) | 2006-01-20 | 2014-07-15 | Clarity Medical Systems, Inc. | Ophthalmic wavefront sensor operating in parallel sampling and lock-in detection mode |
| US9101292B2 (en) | 2006-01-20 | 2015-08-11 | Clarity Medical Systems, Inc. | Apparatus and method for operating a real time large dipoter range sequential wavefront sensor |
| US7445335B2 (en) | 2006-01-20 | 2008-11-04 | Clarity Medical Systems, Inc. | Sequential wavefront sensor |
| US8356900B2 (en) | 2006-01-20 | 2013-01-22 | Clarity Medical Systems, Inc. | Large diopter range real time sequential wavefront sensor |
| EP2026693B1 (en) | 2006-02-14 | 2019-07-31 | Shui T. Lai | Subjective refraction device for correcting low and higher order aberrations |
| US7726811B2 (en) | 2006-02-14 | 2010-06-01 | Lai Shui T | Subjective wavefront refraction using continuously adjustable wave plates of Zernike function |
| US8454160B2 (en) | 2006-02-24 | 2013-06-04 | Amo Development, Llc | Zone extension systems and methods |
| US7717562B2 (en) * | 2006-02-24 | 2010-05-18 | Amo Development Llc. | Scaling Zernike coefficients to smaller pupil sizes for refractive treatments |
| US8474974B2 (en) | 2006-02-24 | 2013-07-02 | Amo Development Llc. | Induced high order aberrations corresponding to geometrical transformations |
| US7695136B2 (en) * | 2007-08-01 | 2010-04-13 | Amo Development, Llc. | Wavefront refractions and high order aberration correction when wavefront maps involve geometrical transformations |
| EP1999443B1 (en) * | 2006-03-14 | 2017-12-27 | AMO Manufacturing USA, LLC | Spatial frequency wavefront sensor system and method |
| JP2007252402A (en) * | 2006-03-20 | 2007-10-04 | Topcon Corp | Ophthalmic apparatus |
| EP1996066B1 (en) * | 2006-03-23 | 2012-10-17 | AMO Manufacturing USA, LLC | System and methods for wavefront reconstruction for aperture with arbitrary shape |
| WO2007127291A2 (en) * | 2006-04-24 | 2007-11-08 | Physical Sciences, Inc. | Stabilized retinal imaging with adaptive optics |
| US8771261B2 (en) * | 2006-04-28 | 2014-07-08 | Topcon Medical Laser Systems, Inc. | Dynamic optical surgical system utilizing a fixed relationship between target tissue visualization and beam delivery |
| CA2649065A1 (en) * | 2006-05-01 | 2007-11-15 | Physical Sciences, Inc. | Hybrid spectral domain optical coherence tomography line scanning laser ophthalmoscope |
| US7791734B2 (en) * | 2006-05-02 | 2010-09-07 | Lawrence Livermore National Security, Llc | High-resolution retinal imaging using adaptive optics and Fourier-domain optical coherence tomography |
| US20080273166A1 (en) | 2007-05-04 | 2008-11-06 | William Kokonaski | Electronic eyeglass frame |
| WO2007124602A1 (en) * | 2006-05-03 | 2007-11-08 | Campbell Melanie C W | Method and device for delivering localized light energy to the eye |
| WO2008088571A2 (en) * | 2006-05-08 | 2008-07-24 | Lai Shui T | Subjective wavefront refraction using continuously adjustable wave plates of zernike function |
| US7656509B2 (en) | 2006-05-24 | 2010-02-02 | Pixeloptics, Inc. | Optical rangefinder for an electro-active lens |
| US7537339B2 (en) * | 2006-05-25 | 2009-05-26 | Synergeyes, Inc. | Hybrid contact lens system and method of fitting |
| EP2030073B1 (en) | 2006-06-23 | 2018-12-05 | Mitsui Chemicals, Inc. | Electronic adapter for electro-active spectacle lenses |
| US20080004698A1 (en) * | 2006-06-30 | 2008-01-03 | Alcon, Inc. | Correction of surgically-induced astigmatism during intraocular lens implants |
| US9955867B2 (en) | 2006-07-26 | 2018-05-01 | Shui T. Lai | Intrastromal surgery correcting low order and high order aberrations of the eye |
| DE102006036086A1 (en) * | 2006-08-02 | 2008-02-07 | Bausch & Lomb Incorporated | Method and apparatus for calculating a laser shot file for use in a refractive excimer laser |
| DE102006036085A1 (en) * | 2006-08-02 | 2008-02-07 | Bausch & Lomb Incorporated | Method and apparatus for calculating a laser shot file for use in an excimer laser |
| US20080212024A1 (en) * | 2006-09-18 | 2008-09-04 | Lai Shui T | Customized contact lenses for reducing aberrations of the eye |
| US20080074611A1 (en) * | 2006-09-22 | 2008-03-27 | Meyers William E | Hybrid contact lens with improved resistance to flexure and method for designing the same |
| US20080084541A1 (en) * | 2006-10-06 | 2008-04-10 | Ming Lai | Ophthalmic system and method |
| WO2008057200A2 (en) * | 2006-10-27 | 2008-05-15 | Pixeloptics, Inc. | Spectacle temple for lens |
| US8152300B2 (en) | 2006-12-19 | 2012-04-10 | Novartis Ag | Premium vision ophthalmic lenses |
| DE102006061933A1 (en) | 2006-12-21 | 2008-06-26 | Carl Zeiss Meditec Ag | Optical system for a fundus camera |
| WO2008083015A2 (en) * | 2006-12-31 | 2008-07-10 | Novartis Ag | Method and system for determining power profile for an eye |
| US20110319875A1 (en) * | 2007-01-19 | 2011-12-29 | Frieder Loesel | Apparatus and Method for Morphing a Three-Dimensional Target Surface into a Two-Dimensional Image for Use in Guiding a Laser Beam in Ocular Surgery |
| AR064985A1 (en) | 2007-01-22 | 2009-05-06 | E Vision Llc | FLEXIBLE ELECTROACTIVE LENS |
| US9398949B2 (en) * | 2007-01-29 | 2016-07-26 | Emmetropia, Inc. | Intraocular lens system |
| US8066769B2 (en) | 2007-01-29 | 2011-11-29 | Werblin Research & Development Corp. | Intraocular lens system |
| US8066768B2 (en) | 2007-01-29 | 2011-11-29 | Werblin Research & Development Corp. | Intraocular lens system |
| US7811320B2 (en) * | 2007-01-29 | 2010-10-12 | Werblin Research & Development Corp. | Intraocular lens system |
| US9427357B2 (en) | 2007-02-21 | 2016-08-30 | Amo Development, Llc | Preformed lens systems and methods |
| US8215770B2 (en) | 2007-02-23 | 2012-07-10 | E-A Ophthalmics | Ophthalmic dynamic aperture |
| CA2678506C (en) * | 2007-02-23 | 2016-10-18 | Mimo Ag | Ophthalmologic apparatus for imaging an eye by optical coherence tomography |
| CN101254091B (en) * | 2007-02-28 | 2010-08-18 | 深圳大学 | Method for implementing high spatial discrimination retina image-forming with second harmonics and two-photon fluorescence excitation |
| US20090091818A1 (en) * | 2007-10-05 | 2009-04-09 | Haddock Joshua N | Electro-active insert |
| US7883207B2 (en) | 2007-12-14 | 2011-02-08 | Pixeloptics, Inc. | Refractive-diffractive multifocal lens |
| US7883206B2 (en) | 2007-03-07 | 2011-02-08 | Pixeloptics, Inc. | Multifocal lens having a progressive optical power region and a discontinuity |
| US20080273169A1 (en) | 2007-03-29 | 2008-11-06 | Blum Ronald D | Multifocal Lens Having a Progressive Optical Power Region and a Discontinuity |
| TWI407971B (en) * | 2007-03-30 | 2013-09-11 | Nitto Denko Corp | Cancer cells and tumor-related fibroblasts |
| DE102007017611A1 (en) | 2007-04-12 | 2008-10-16 | SCHRÜNDER, Stephan | Method and system for eye measurement |
| CN101292862B (en) * | 2007-04-25 | 2012-02-29 | 江阴龙跃信息科技有限公司 | Retina cell microscopic imaging system |
| CA2685355A1 (en) * | 2007-04-27 | 2008-11-06 | The Institute For Eye Research Limited | Determination of optical adjustments for retarding myopia progression |
| US10613355B2 (en) | 2007-05-04 | 2020-04-07 | E-Vision, Llc | Moisture-resistant eye wear |
| US11061252B2 (en) | 2007-05-04 | 2021-07-13 | E-Vision, Llc | Hinge for electronic spectacles |
| US8016420B2 (en) | 2007-05-17 | 2011-09-13 | Amo Development Llc. | System and method for illumination and fixation with ophthalmic diagnostic instruments |
| CA2688170C (en) | 2007-05-24 | 2016-10-18 | Amo Development, Llc | Accommodation compensation systems and methods |
| US7828432B2 (en) | 2007-05-25 | 2010-11-09 | Synergeyes, Inc. | Hybrid contact lenses prepared with expansion controlled polymeric materials |
| US8486055B2 (en) * | 2007-06-26 | 2013-07-16 | Bausch & Lomb Incorporated | Method for modifying the refractive index of ocular tissues |
| US7976163B2 (en) | 2007-06-27 | 2011-07-12 | Amo Wavefront Sciences Llc | System and method for measuring corneal topography |
| US7988290B2 (en) * | 2007-06-27 | 2011-08-02 | AMO Wavefront Sciences LLC. | Systems and methods for measuring the shape and location of an object |
| US8317321B2 (en) | 2007-07-03 | 2012-11-27 | Pixeloptics, Inc. | Multifocal lens with a diffractive optical power region |
| US8550625B2 (en) | 2007-08-01 | 2013-10-08 | Amo Development, Llc | Systems and methods for fine-tuning refractive surgery |
| US9192296B2 (en) | 2007-08-21 | 2015-11-24 | Visionix Ltd. | Multifunctional ophthalmic measurement system |
| CN101772696A (en) * | 2007-08-27 | 2010-07-07 | 株式会社尼康 | Wavefront aberration measuring device and method and wavefront aberration adjusting method |
| US8974526B2 (en) | 2007-08-27 | 2015-03-10 | Amo Groningen B.V. | Multizonal lens with extended depth of focus |
| ES2528651T3 (en) | 2007-09-05 | 2015-02-11 | Alcon Lensx, Inc. | Laser induced protection screen in laser surgery |
| US8764737B2 (en) | 2007-09-06 | 2014-07-01 | Alcon Lensx, Inc. | Precise targeting of surgical photodisruption |
| US9456925B2 (en) | 2007-09-06 | 2016-10-04 | Alcon Lensx, Inc. | Photodisruptive laser treatment of the crystalline lens |
| US20100324543A1 (en) * | 2007-09-18 | 2010-12-23 | Kurtz Ronald M | Method And Apparatus For Integrating Cataract Surgery With Glaucoma Or Astigmatism Surgery |
| US8333474B2 (en) | 2007-10-19 | 2012-12-18 | Wavetec Vision Systems, Inc. | Optical instrument alignment system |
| US7594729B2 (en) | 2007-10-31 | 2009-09-29 | Wf Systems, Llc | Wavefront sensor |
| US20100324542A1 (en) * | 2007-11-02 | 2010-12-23 | Kurtz Ronald M | Method to Guide a Cataract Procedure by Corneal Imaging |
| US9395534B2 (en) * | 2007-11-27 | 2016-07-19 | Wisconsin Alumni Research Foundation | Optical system for correction of tissue induced aberration |
| US7874674B2 (en) * | 2007-12-12 | 2011-01-25 | Allred Lloyd G | Aberrometer having reduced noise |
| US7802883B2 (en) | 2007-12-20 | 2010-09-28 | Johnson & Johnson Vision Care, Inc. | Cosmetic contact lenses having a sparkle effect |
| ES2537205T3 (en) | 2008-01-09 | 2015-06-03 | Alcon Lensx, Inc. | Photodisruptor laser tissue fragmentation |
| CA2718521A1 (en) | 2008-03-18 | 2009-09-24 | Pixeloptics, Inc. | Advanced electro-active optic device |
| US8154804B2 (en) | 2008-03-25 | 2012-04-10 | E-Vision Smart Optics, Inc. | Electro-optic lenses for correction of higher order aberrations |
| WO2010064150A2 (en) * | 2008-04-04 | 2010-06-10 | Amo Regional Holdings | Systems and methods for determing intraocular lens power |
| WO2009132104A1 (en) * | 2008-04-22 | 2009-10-29 | Amo Development Llc | High-order optical correction during corneal laser surgery |
| JP5306041B2 (en) * | 2008-05-08 | 2013-10-02 | キヤノン株式会社 | Imaging apparatus and method thereof |
| DE102008026576A1 (en) * | 2008-05-30 | 2009-12-03 | Carl Zeiss Meditec Ag | Optical system for ophthalmological devices, in particular fundus cameras |
| US8529557B2 (en) * | 2008-05-30 | 2013-09-10 | Technolas Perfect Vision Gmbh | System and method for stray light compensation of corneal cuts |
| DE102008028509A1 (en) * | 2008-06-16 | 2009-12-24 | Technolas Gmbh Ophthalmologische Systeme | Treatment pattern monitoring device |
| WO2010000279A1 (en) | 2008-06-30 | 2010-01-07 | Wavelight Ag | Device for ophthalmologic, particularly refractive, laser surgery |
| DE102008035995A1 (en) * | 2008-08-01 | 2010-02-04 | Technolas Perfect Vision Gmbh | Combination of excimer laser ablation and femtosecond laser technique |
| EP2330967A1 (en) * | 2008-08-28 | 2011-06-15 | Technolas Perfect Vision GmbH | Eye measurement and modeling techniques |
| US8020994B2 (en) * | 2008-09-04 | 2011-09-20 | Heidelberg Engineering Gmbh | Custom phase plate |
| US7988295B2 (en) | 2008-10-28 | 2011-08-02 | Heidelberg Engineering Gmbh | Laser control with phase plate feedback |
| DE102008053827A1 (en) | 2008-10-30 | 2010-05-12 | Technolas Perfect Vision Gmbh | Apparatus and method for providing a laser shot file |
| US8550624B2 (en) | 2008-11-06 | 2013-10-08 | Wavetec Vision Systems, Inc. | Optical angular measurement system for ophthalmic applications and method for positioning of a toric intraocular lens with increased accuracy |
| US8254724B2 (en) * | 2008-11-06 | 2012-08-28 | Bausch & Lomb Incorporated | Method and apparatus for making and processing aberration measurements |
| US7695135B1 (en) | 2008-11-11 | 2010-04-13 | Boston Foundation For Sight | Scleral lens with scalloped channels or circumferential fenestrated channels |
| US7980698B2 (en) | 2008-11-19 | 2011-07-19 | Bausch & Lomb Incorporated | Power-adjusted aberrometer |
| EP2369972B1 (en) | 2008-12-01 | 2017-06-07 | Perfect Vision Technology (HK) Ltd. | Methods and devices for refractive correction of eyes |
| US9277863B2 (en) | 2008-12-01 | 2016-03-08 | Perfect Vision Technology (Hk) Ltd. | Methods and systems for automated measurement of the eyes and delivering of sunglasses and eyeglasses |
| US9649032B2 (en) | 2008-12-01 | 2017-05-16 | Perfect Vision Technology (Hk) Ltd. | Systems and methods for remote measurement of the eyes and delivering of sunglasses and eyeglasses |
| JP5555258B2 (en) * | 2009-01-15 | 2014-07-23 | フィジカル サイエンシーズ， インコーポレイテッド | Adaptive optical scanning ophthalmoscope and method |
| WO2010085618A1 (en) * | 2009-01-23 | 2010-07-29 | Indiana University Research And Technology Corporation | Devices and methods for polarization-sensitive optical coherence tomography with adaptive optics |
| WO2010093908A2 (en) * | 2009-02-12 | 2010-08-19 | University Of Rochester | Aberration control by corneal collagen crosslinking combined with beam-shaping technique |
| US8137271B2 (en) * | 2009-03-04 | 2012-03-20 | Heidelberg Engineering Gmbh | System and method for assessing risk of glaucoma onset |
| ES2346392B1 (en) | 2009-03-04 | 2011-10-03 | Voptica, S.L. | METHOD OF MEASUREMENT AND BINOCULAR CONTROL OF EYE ABERRATIONS, SIMULTANEOUS PRESENTATION OF VISUAL STIMULES, AND OPHTHALMIC INSTRUMENT THAT IMPLEMENTS SUCH METHOD. |
| JP5676856B2 (en) * | 2009-05-08 | 2015-02-25 | キヤノン株式会社 | Image acquisition device with adaptive optics |
| US8876290B2 (en) * | 2009-07-06 | 2014-11-04 | Wavetec Vision Systems, Inc. | Objective quality metric for ocular wavefront measurements |
| KR101730675B1 (en) | 2009-07-14 | 2017-05-11 | 웨이브텍 비젼 시스템스, 인크. | Ophthalmic surgery measurement system |
| ES2653970T3 (en) | 2009-07-14 | 2018-02-09 | Wavetec Vision Systems, Inc. | Determination of the effective position of the lens of an intraocular lens using aphakic refractive power |
| JP5624040B2 (en) | 2009-08-04 | 2014-11-12 | 国立大学法人宇都宮大学 | 3D image generation device for retina |
| JP5483996B2 (en) * | 2009-10-23 | 2014-05-07 | キヤノン株式会社 | Compensating optical device, imaging device, and compensating optical method |
| JP5553635B2 (en) * | 2009-10-23 | 2014-07-16 | キヤノン株式会社 | Compensating optical device, imaging device, compensating optical method, and imaging method |
| US9492322B2 (en) * | 2009-11-16 | 2016-11-15 | Alcon Lensx, Inc. | Imaging surgical target tissue by nonlinear scanning |
| JP5511324B2 (en) * | 2009-11-17 | 2014-06-04 | キヤノン株式会社 | Compensating optical device, compensating optical method, imaging device, and imaging method |
| JP5511323B2 (en) * | 2009-11-17 | 2014-06-04 | キヤノン株式会社 | Compensating optical device, compensating optical method, imaging device, and imaging method |
| JP5517571B2 (en) * | 2009-11-18 | 2014-06-11 | キヤノン株式会社 | Imaging apparatus and imaging method |
| EP2525706A2 (en) * | 2010-01-21 | 2012-11-28 | Physical Sciences, Inc. | Multi-functional adaptive optics retinal imaging |
| US8265364B2 (en) | 2010-02-05 | 2012-09-11 | Alcon Lensx, Inc. | Gradient search integrated with local imaging in laser surgical systems |
| EP2533680B1 (en) * | 2010-02-12 | 2018-05-30 | Johnson & Johnson Vision Care Inc. | Apparatus to obtain clinical ophthalmic high order optical aberrations |
| US8414564B2 (en) | 2010-02-18 | 2013-04-09 | Alcon Lensx, Inc. | Optical coherence tomographic system for ophthalmic surgery |
| CN101840193B (en) * | 2010-03-25 | 2013-03-06 | 苏州大学 | Method for manufacturing holographic grating |
| US8409178B2 (en) | 2010-03-30 | 2013-04-02 | Amo Development Llc. | Systems and methods for evaluating treatment tables for refractive surgery |
| US9642518B2 (en) | 2010-03-30 | 2017-05-09 | Amo Development, Llc | Random eye generation systems and methods |
| DE102010019805A1 (en) * | 2010-05-06 | 2011-11-10 | Z/I Imaging Ltd. | Camera, in particular for taking aerial photographs from airplanes |
| JP5545984B2 (en) * | 2010-05-31 | 2014-07-09 | 株式会社ニデック | Fundus imaging device with wavefront compensation |
| US8398236B2 (en) | 2010-06-14 | 2013-03-19 | Alcon Lensx, Inc. | Image-guided docking for ophthalmic surgical systems |
| DE102010024606B4 (en) * | 2010-06-22 | 2019-11-14 | Carl Zeiss Meditec Ag | Aberrometric measuring system |
| CN101869466B (en) * | 2010-07-13 | 2012-07-18 | 苏州微清医疗器械有限公司 | Confocal scanning and optical coherence tomograph based on self-adaptive optical technology |
| CN102028449B (en) * | 2010-08-16 | 2012-12-12 | 苏州六六视觉科技股份有限公司 | Human eye retina imaging system and method capable of carrying out layered imaging |
| US9532708B2 (en) | 2010-09-17 | 2017-01-03 | Alcon Lensx, Inc. | Electronically controlled fixation light for ophthalmic imaging systems |
| WO2012040196A1 (en) | 2010-09-20 | 2012-03-29 | Amo Development Llc | System and methods for mitigating changes in pupil size during laser refractive surgery to maintain ablation centration |
| US8439902B2 (en) * | 2010-09-30 | 2013-05-14 | Wavelight Gmbh | Apparatus and method for processing material with focused electromagnetic radiation |
| US10783999B2 (en) | 2010-10-05 | 2020-09-22 | Amo Development, Llc | Basis data evaluation systems and methods |
| US20120083776A1 (en) | 2010-10-05 | 2012-04-05 | Amo Development, Llc | Annular and other ablation profiles for refractive surgery systems and methods |
| GB2485175A (en) * | 2010-11-03 | 2012-05-09 | Univ City | Optical imaging system using incoherent light and interference fringes |
| JP5727197B2 (en) * | 2010-11-04 | 2015-06-03 | 株式会社ニデック | Fundus imaging device with wavefront compensation |
| US8801178B2 (en) | 2010-11-04 | 2014-08-12 | Nidek Co., Ltd. | Fundus photographing apparatus |
| WO2012073112A1 (en) | 2010-12-01 | 2012-06-07 | Amo Groningen B.V. | A multifocal lens having an optical add power progression, and a system and method of providing same |
| US9931200B2 (en) | 2010-12-17 | 2018-04-03 | Amo Groningen B.V. | Ophthalmic devices, systems, and methods for optimizing peripheral vision |
| JP5731815B2 (en) | 2010-12-20 | 2015-06-10 | キヤノン株式会社 | Imaging method, imaging apparatus, and program |
| WO2012088424A1 (en) * | 2010-12-23 | 2012-06-28 | The Trustees Of Columbia University In The City Of New York | Lensless retinal camera apparatus and method |
| US10582846B2 (en) | 2010-12-30 | 2020-03-10 | Amo Wavefront Sciences, Llc | Method and system for eye measurements and cataract surgery planning using vector function derived from prior surgeries |
| EP3213724B1 (en) | 2010-12-30 | 2019-09-18 | Amo Wavefront Sciences, LLC | Improved treatment planning method and system for controlling laser refractive surgery |
| US10583039B2 (en) | 2010-12-30 | 2020-03-10 | Amo Wavefront Sciences, Llc | Method and system for eye measurements and cataract surgery planning using vector function derived from prior surgeries |
| US10582847B2 (en) | 2010-12-30 | 2020-03-10 | Amo Wavefront Sciences, Llc | Method and system for eye measurements and cataract surgery planning using vector function derived from prior surgeries |
| US9501621B2 (en) | 2011-03-18 | 2016-11-22 | Amo Development, Llc | Treatment validation systems and methods |
| EP3170475B1 (en) * | 2011-03-24 | 2018-10-31 | Kowa Company Ltd. | Intraocular lens |
| US9895058B2 (en) | 2011-03-25 | 2018-02-20 | Carl Zeiss Meditec Ag | Heads-up vision analyzer |
| JP5220208B2 (en) | 2011-03-31 | 2013-06-26 | キヤノン株式会社 | Control device, imaging control method, and program |
| US8459794B2 (en) | 2011-05-02 | 2013-06-11 | Alcon Lensx, Inc. | Image-processor-controlled misalignment-reduction for ophthalmic systems |
| US9622913B2 (en) | 2011-05-18 | 2017-04-18 | Alcon Lensx, Inc. | Imaging-controlled laser surgical system |
| US10813791B2 (en) | 2011-06-02 | 2020-10-27 | University Of Rochester | Method for modifying the refractive index of ocular tissues and applications thereof |
| US9521949B2 (en) | 2011-06-23 | 2016-12-20 | Amo Development, Llc | Ophthalmic range finding |
| CA3133258A1 (en) | 2011-06-23 | 2012-12-27 | Amo Development, Llc | Ophthalmic range finding |
| US8978660B2 (en) | 2011-07-21 | 2015-03-17 | Amo Development, Llc | Tilt compensation, measurement, and associated adjustment of refractive prescriptions during surgical and other treatments of the eye |
| RU2482525C2 (en) * | 2011-08-17 | 2013-05-20 | Федеральное государственное бюджетное учреждение науки Специальная астрофизическая обсерватория Российской академии наук | Wave front inclination compensator mechanism |
| US8398238B1 (en) | 2011-08-26 | 2013-03-19 | Alcon Lensx, Inc. | Imaging-based guidance system for ophthalmic docking using a location-orientation analysis |
| EP2570073A1 (en) | 2011-09-02 | 2013-03-20 | Nidek Co., Ltd. | Fundus photographing apparatus with wavefront compensation |
| EP2596745B1 (en) * | 2011-10-07 | 2019-06-19 | Popovic, Zoran | Reference calibration for an adaptive optics system |
| WO2013053938A1 (en) | 2011-10-14 | 2013-04-18 | Amo Groningen B.V. | Apparatus, system and method to account for spherical aberration at the iris plane in the design of an intraocular lens |
| RU2502212C2 (en) * | 2011-11-25 | 2013-12-20 | Виктор Ильич Бетчер | Method of forming image on display of digital device |
| WO2013082466A1 (en) | 2011-11-30 | 2013-06-06 | Amo Development, Llc. | System and method for ophthalmic surface measurements based on sequential estimates |
| US9066784B2 (en) | 2011-12-19 | 2015-06-30 | Alcon Lensx, Inc. | Intra-surgical optical coherence tomographic imaging of cataract procedures |
| US9023016B2 (en) | 2011-12-19 | 2015-05-05 | Alcon Lensx, Inc. | Image processor for intra-surgical optical coherence tomographic imaging of laser cataract procedures |
| KR20230020587A (en) | 2012-01-06 | 2023-02-10 | 이-비전 스마트 옵틱스, 아이엔씨. | Eyewear docking station and electronic module |
| CN102589720B (en) * | 2012-03-19 | 2014-01-01 | 中国科学院光电技术研究所 | Hartmann wavefront measuring instrument suitable for non-uniform light illumination |
| TWI588560B (en) | 2012-04-05 | 2017-06-21 | 布萊恩荷登視覺協會 | Lenses, devices, methods and systems for refractive error |
| CN104394755B (en) | 2012-04-30 | 2017-12-12 | 透明医疗体系公司 | The ophthalmology Wavefront sensor operated in parallel sampling and lock-in detection pattern |
| JP6041540B2 (en) * | 2012-06-01 | 2016-12-07 | キヤノン株式会社 | Ophthalmic equipment |
| US10175476B2 (en) * | 2012-07-16 | 2019-01-08 | Trustees Of Boston University | Solid immersion microscopy system with deformable mirror for correction of aberrations |
| EP2874584B1 (en) | 2012-07-20 | 2016-05-25 | AMO Manufacturing USA, LLC | Systems and methods for correcting high order aberrations in laser refractive surgery |
| WO2014031490A1 (en) * | 2012-08-24 | 2014-02-27 | Advanced Micro Devices, Inc. | Laser scanning module including an optical isolator |
| CN108013952A (en) | 2012-08-31 | 2018-05-11 | Amo格罗宁根私人有限公司 | Polycyclic crystalline lens, system and method for extended focal depth |
| US9072462B2 (en) * | 2012-09-27 | 2015-07-07 | Wavetec Vision Systems, Inc. | Geometric optical power measurement device |
| WO2014055690A1 (en) | 2012-10-02 | 2014-04-10 | Amo Development, Llc. | Systems and methods for treatment target deconvolution |
| US9201250B2 (en) | 2012-10-17 | 2015-12-01 | Brien Holden Vision Institute | Lenses, devices, methods and systems for refractive error |
| CN102860816B (en) * | 2012-10-12 | 2014-10-29 | 中国科学院光电技术研究所 | Human eye retina three-dimensional imaging device based on double wavefront correctors |
| US9541773B2 (en) | 2012-10-17 | 2017-01-10 | Brien Holden Vision Institute | Lenses, devices, methods and systems for refractive error |
| GB2509131B (en) * | 2012-12-21 | 2017-05-17 | Optos Plc | Improvements in and relating to ophthalmoscopes |
| AU2014228357B2 (en) | 2013-03-11 | 2018-08-23 | Johnson & Johnson Surgical Vision, Inc. | Intraocular lens that matches an image surface to a retinal shape, and method of designing same |
| WO2014152707A1 (en) * | 2013-03-15 | 2014-09-25 | Blanco Austin | System and method for rejecting afocal light collected from an in vivo human retina |
| WO2014149839A1 (en) | 2013-03-15 | 2014-09-25 | Amo Wavefront Sciences, Llc | Angular multiplexed optical coherence tomography systems and methods |
| CN103385691B (en) * | 2013-08-02 | 2015-07-15 | 中国科学院光电技术研究所 | Binocular adaptive optical vision simulator and simulation method |
| CN103393400A (en) * | 2013-08-06 | 2013-11-20 | 中国科学院光电技术研究所 | Scanning type living human eye retina high-resolution imaging system |
| CN103431837B (en) * | 2013-08-23 | 2015-04-29 | 饶丰 | Human eye axial chromatic aberration and transverse chromatic aberration measurement device based on Hartmann sensor and method thereof |
| US9357912B2 (en) | 2013-09-09 | 2016-06-07 | Yan Zhang | Apparatus and method for characterizing biomechanical properties of eye tissue |
| AU2014346484A1 (en) | 2013-11-07 | 2016-01-07 | Amo Development Llc | Treatment validation systems and methods |
| EP3089716B1 (en) | 2013-12-31 | 2019-07-24 | AMO Development, LLC | Wavefront measurement pre-smoothing systems and methods |
| EP3116440B1 (en) | 2014-03-10 | 2024-08-28 | Amo Groningen B.V. | Enhanced toric lens that improves overall vision where there is a local loss of retinal function |
| EP3134031B1 (en) | 2014-04-21 | 2024-08-28 | Amo Groningen B.V. | An intraocular lens |
| JP6905463B2 (en) | 2014-07-02 | 2021-07-21 | アイディーエックス，エルエルシー | A device and method for adjusting the alignment between the subject's eye and the optical axis of the eyepiece imaging device. |
| US10952606B2 (en) | 2014-07-02 | 2021-03-23 | Amo Development, Llc | Optical measurement system and method including blink rate monitor and/or tear film breakup detector |
| EP3284394A1 (en) | 2014-07-02 | 2018-02-21 | AMO WaveFront Sciences, LLC | Optical measurment system and method including blink rate monitor and/or tear film breakup detector |
| EP3272275A1 (en) | 2014-07-03 | 2018-01-24 | AMO WaveFront Sciences, LLC | Optical measurement system and method with target brightness level adjustment |
| US20160038277A1 (en) | 2014-08-11 | 2016-02-11 | Amo Development, Llc | Optical Surface Systems and Methods for Treatment of Presbyopia and Other Vision Conditions |
| DE102014112199B4 (en) | 2014-08-26 | 2024-10-10 | Carl Zeiss Microscopy Gmbh | Microscopic imaging system |
| JP6442960B2 (en) | 2014-09-30 | 2018-12-26 | 株式会社ニデック | Fundus imaging device with wavefront compensation |
| CA2973345A1 (en) | 2015-01-09 | 2016-07-14 | Amo Development, Llc | Vergence weighting systems and methods for treatment of presbyopia and other vision conditions |
| EP3253275B1 (en) | 2015-02-06 | 2019-10-23 | AMO WaveFront Sciences, LLC | Systems and methods of optical coherence tomography with a multi-focal delay line |
| JP6608153B2 (en) * | 2015-03-30 | 2019-11-20 | 蛇の目ミシン工業株式会社 | Servo press, control method and program |
| CN104783755A (en) * | 2015-04-29 | 2015-07-22 | 中国科学院光电技术研究所 | Adaptive optical retinal imaging apparatus and method |
| KR101716125B1 (en) * | 2015-07-20 | 2017-03-15 | 주식회사 토모큐브 | Method and Apparatus for Measuring 3D Refractive Index Tomograms Using a High-Speed Wavefront Shaper |
| WO2017019117A1 (en) | 2015-07-27 | 2017-02-02 | Amo Wavefront Sciences, Llc | Optical imaging and measurement systems and methods for cataract surgery and treatment planning |
| WO2017059291A1 (en) | 2015-10-01 | 2017-04-06 | Amo Wavefront Sciences, Llc | Optical measurement systems and methods with custom chromatic aberration adjustments |
| US10820794B2 (en) | 2015-11-06 | 2020-11-03 | Canon Kabushiki Kaisha | Pupil monitoring method for adaptive optics imaging system |
| EP3380051A1 (en) | 2015-11-23 | 2018-10-03 | AMO WaveFront Sciences, LLC | Method and system for eye measurements and cataract surgery planning using vector function derived from prior surgeries |
| AU2017218681B2 (en) | 2016-02-09 | 2021-09-23 | Amo Groningen B.V. | Progressive power intraocular lens, and methods of use and manufacture |
| US10588738B2 (en) | 2016-03-11 | 2020-03-17 | Amo Groningen B.V. | Intraocular lenses that improve peripheral vision |
| US10599006B2 (en) | 2016-04-12 | 2020-03-24 | E-Vision Smart Optics, Inc. | Electro-active lenses with raised resistive bridges |
| CN114815435A (en) | 2016-04-12 | 2022-07-29 | E-视觉智能光学公司 | Electroactive lens with raised resistive bridge |
| DE102016106953A1 (en) | 2016-04-14 | 2017-10-19 | Arnold & Richter Cine Technik Gmbh & Co. Betriebs Kg | camera viewfinder |
| AU2017252020B2 (en) | 2016-04-19 | 2021-11-11 | Amo Groningen B.V. | Ophthalmic devices, system and methods that improve peripheral vision |
| US10444539B2 (en) | 2016-05-11 | 2019-10-15 | Perect Vision Technology (Hk) Ltd. | Methods and systems for determining refractive corrections of human eyes for eyeglasses |
| JP7017002B2 (en) * | 2016-06-16 | 2022-02-08 | ハダシット メディカル リサーチ サービシズ アンド ディベラップメント リミテッド | Devices and methods for determining pupil size in subjects with closed eyelids |
| EP3782591B1 (en) | 2016-07-07 | 2023-11-29 | AMO Development, LLC | Lenticular laser incision using wavefront guided maps |
| US10327952B2 (en) | 2016-08-31 | 2019-06-25 | Amo Development, Llc | Ultraviolet radiation sensor systems and methods for laser pulse energy control in eye surgery |
| CA3035761A1 (en) | 2016-09-06 | 2018-03-15 | Amo Wavefront Sciences, Llc | Optical measurement systems and processes with wavefront aberrometer having variable focal length lens |
| US20180064576A1 (en) | 2016-09-08 | 2018-03-08 | Amo Development, Llc | Systems and methods for obtaining iris registration and pupil centration for laser surgery |
| CA3043514A1 (en) | 2016-11-09 | 2018-05-17 | Amo Wavefront Sciences, Llc | Optical coherence tomography systems and methods with dispersion compensation |
| WO2018102624A1 (en) | 2016-12-01 | 2018-06-07 | Amo Development, Llc | Spherical aberration reduction systems and methods |
| US10060872B1 (en) | 2017-02-13 | 2018-08-28 | General Electric Company | Sensing system and method |
| US20180235809A1 (en) | 2017-02-22 | 2018-08-23 | Amo Development Llc | Transition zone systems and methods |
| WO2018160711A1 (en) | 2017-02-28 | 2018-09-07 | Amo Wavefront Sciences, Llc | Method and system for pupil retro illumination using sample arm of oct interferometer |
| SG11201908581YA (en) * | 2017-03-15 | 2019-10-30 | Univ Queensland Technology | Apparatus, method and system for measuring the influence of ophthalmic lens design |
| US11497599B2 (en) | 2017-03-17 | 2022-11-15 | Amo Groningen B.V. | Diffractive intraocular lenses for extended range of vision |
| US11523897B2 (en) | 2017-06-23 | 2022-12-13 | Amo Groningen B.V. | Intraocular lenses for presbyopia treatment |
| AU2018292030B2 (en) | 2017-06-28 | 2024-02-08 | Amo Groningen B.V. | Extended range and related intraocular lenses for presbyopia treatment |
| EP3646110A1 (en) | 2017-06-28 | 2020-05-06 | Amo Groningen B.V. | Diffractive lenses and related intraocular lenses for presbyopia treatment |
| US11327210B2 (en) | 2017-06-30 | 2022-05-10 | Amo Groningen B.V. | Non-repeating echelettes and related intraocular lenses for presbyopia treatment |
| US11000362B2 (en) | 2017-09-11 | 2021-05-11 | Amo Groningen B.V. | Intraocular lenses with customized add power |
| US10973685B2 (en) | 2017-12-01 | 2021-04-13 | Amo Development, Llc | Systems and methods for reducing spherical aberration using periphery modification |
| EP3743679B1 (en) | 2018-01-23 | 2023-06-28 | AMO Development, LLC | Methods and systems of optical coherence tomography with fiducial signal for correcting scanning laser nonlinearity |
| US11571336B2 (en) * | 2018-01-26 | 2023-02-07 | University Of Rochester | Refractive index shaping laser writing process control |
| US11311187B2 (en) | 2018-04-06 | 2022-04-26 | Amo Development, Llc | Methods and systems for corneal topography with in-focus scleral imaging |
| WO2019194851A1 (en) * | 2018-04-06 | 2019-10-10 | Perfect Vision Technology (Hk) Ltd. | Methods and systems of refraction automation for prescribing eyeglasses |
| US11246484B2 (en) | 2018-08-20 | 2022-02-15 | Amo Development, Llc | Methods and systems for eye measurement with in-focus iris and scleral imaging |
| US11006823B2 (en) | 2019-01-28 | 2021-05-18 | Amo Development, Llc | Methods and systems for optical coherence tomography scanning of cornea and retina |
| DE102019115931A1 (en) * | 2019-06-12 | 2020-12-17 | Carl Zeiss Microscopy Gmbh | Optical arrangement for a microscope |
| US11266495B2 (en) | 2019-10-20 | 2022-03-08 | Rxsight, Inc. | Light adjustable intraocular lens with a modulable absorption front protection layer |
| EP4076134A1 (en) | 2019-12-20 | 2022-10-26 | AMO Development, LLC | Optical measurement systems and processes with non-telecentric projection of fixation target to eye |
| EP4081093A1 (en) | 2019-12-23 | 2022-11-02 | AMO Development, LLC | Optical measurement systems and processes with fixation target having cylinder compensation |
| US11886046B2 (en) | 2019-12-30 | 2024-01-30 | Amo Groningen B.V. | Multi-region refractive lenses for vision treatment |
| CA3166308A1 (en) | 2019-12-30 | 2021-07-08 | Amo Groningen B.V. | Lenses having diffractive profiles with irregular width for vision treatment |
| WO2021137032A1 (en) | 2019-12-30 | 2021-07-08 | Amo Development, Llc | Optical measurement systems and processes with fixation target having bokeh compensation |
| US11963722B2 (en) | 2021-04-13 | 2024-04-23 | Amo Development, Llc | Methods and systems for determining change in eye position between successive eye measurements |
| US20220330813A1 (en) | 2021-04-15 | 2022-10-20 | Amo Development, Llc | Methods and systems for thickness measurements using spectrally resolved full gradient topography |
| US12048484B2 (en) | 2021-04-21 | 2024-07-30 | Amo Development, Llc | Compact autocylinder compensation module for autorefractor and autorefractor with autocylinder compensation module |
Family Cites Families (75)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5838839A (en) * | 1981-08-31 | 1983-03-07 | Tokyo Optical Co Ltd | Method and apparatus for measuring refractive index |
| DE3150124C2 (en) * | 1981-12-18 | 1985-01-31 | Fa. Carl Zeiss, 7920 Heidenheim | Device for examining the anterior segments of the eye |
| DE3422144A1 (en) * | 1984-06-14 | 1985-12-19 | Josef Prof. Dr. 6900 Heidelberg Bille | DEVICE FOR DISPLAYING AREA AREAS OF THE HUMAN EYE |
| US4669466A (en) * | 1985-01-16 | 1987-06-02 | Lri L.P. | Method and apparatus for analysis and correction of abnormal refractive errors of the eye |
| US6267756B1 (en) | 1986-03-08 | 2001-07-31 | G. Rodenstock Instrumente Gmbh | Apparatus for the observation and the treatment of the eye using a laser |
| DE3607721A1 (en) | 1986-03-08 | 1987-09-10 | Rodenstock Instr | DEVICE FOR LASER TREATMENT OF THE EYE |
| WO1987005205A1 (en) * | 1986-03-08 | 1987-09-11 | G. Rodenstock Instrumente Gmbh | Laser installation for examining and treating the eye |
| US5177511A (en) * | 1986-11-08 | 1993-01-05 | G. Rodenstock Instruments Gmbh | Apparatus for producing images of an object and in particular for observing the rear portions of the eye |
| US4764930A (en) * | 1988-01-27 | 1988-08-16 | Intelligent Surgical Lasers | Multiwavelength laser source |
| US4881808A (en) * | 1988-02-10 | 1989-11-21 | Intelligent Surgical Lasers | Imaging system for surgical lasers |
| US4848340A (en) * | 1988-02-10 | 1989-07-18 | Intelligent Surgical Lasers | Eyetracker and method of use |
| IT1215851B (en) | 1988-02-11 | 1990-02-22 | Renato Liffredo | INTRAOCULAR LENS WITH CHROMATIC CORRECTION AND ABSORPTION DIAGRAM. |
| EP0349228B1 (en) * | 1988-06-27 | 1995-03-01 | Ryusyo Industrial Co., Ltd. | Apparatus for measuring refractive power of eye |
| DE3821973A1 (en) * | 1988-06-29 | 1990-02-08 | Rodenstock Instr | DEVICE FOR PRODUCING AN IMAGE OF AN OBJECT (III) |
| US5098426A (en) | 1989-02-06 | 1992-03-24 | Phoenix Laser Systems, Inc. | Method and apparatus for precision laser surgery |
| US4991953A (en) * | 1989-02-09 | 1991-02-12 | Eye Research Institute Of Retina Foundation | Scanning laser vitreous camera |
| US5159361A (en) * | 1989-03-09 | 1992-10-27 | Par Technology Corporation | Method and apparatus for obtaining the topography of an object |
| JP2931325B2 (en) * | 1989-06-29 | 1999-08-09 | 興和株式会社 | Ophthalmic measurement device |
| US4991653A (en) * | 1989-11-08 | 1991-02-12 | Halliburton Company | Wash tool |
| DE4002029A1 (en) * | 1990-01-24 | 1991-07-25 | Peter Hoefer | METHOD FOR THE PRODUCTION OF CONTACT LENSES AND CONTACT LENS PRODUCTION SYSTEM |
| JP2854657B2 (en) * | 1990-03-14 | 1999-02-03 | 興和株式会社 | Ophthalmic measurement device |
| US5062702A (en) * | 1990-03-16 | 1991-11-05 | Intelligent Surgical Lasers, Inc. | Device for mapping corneal topography |
| DE69108123T2 (en) * | 1990-06-27 | 1995-07-20 | Framatome Sa | Method and device for disassembling an irradiated component of a nuclear reactor by cutting out its wall. |
| US5490849A (en) | 1990-07-13 | 1996-02-13 | Smith; Robert F. | Uniform-radiation caustic surface for photoablation |
| WO1992001417A1 (en) * | 1990-07-19 | 1992-02-06 | Horwitz Larry S | Vision measurement and correction |
| US5258791A (en) * | 1990-07-24 | 1993-11-02 | General Electric Company | Spatially resolved objective autorefractometer |
| AT395523B (en) * | 1990-07-24 | 1993-01-25 | Spellitz Fritz | OPTICAL MEASURING SYSTEM FOR THE HUMAN CORNUS |
| US5722427A (en) * | 1993-05-10 | 1998-03-03 | Eyesys Technologies, Inc. | Method of refractive surgery |
| US5173723A (en) | 1990-10-02 | 1992-12-22 | Volk Donald A | Aspheric ophthalmic accommodating lens design for intraocular lens and contact lens |
| US5139022A (en) * | 1990-10-26 | 1992-08-18 | Philip Lempert | Method and apparatus for imaging and analysis of ocular tissue |
| US5072993A (en) * | 1990-12-24 | 1991-12-17 | Caterpillar Inc. | Self-contained shim pack assembly |
| US5214456A (en) * | 1991-10-09 | 1993-05-25 | Computed Anatomy Incorporated | Mapping of corneal topography with display of pupil perimeter |
| JP3112108B2 (en) * | 1991-11-26 | 2000-11-27 | 株式会社トプコン | Corneal thickness measuring device |
| US5229889A (en) * | 1991-12-10 | 1993-07-20 | Hughes Aircraft Company | Simple adaptive optical system |
| JPH0559448U (en) * | 1992-01-14 | 1993-08-06 | 松原電機工業株式会社 | Display device |
| US5233174A (en) * | 1992-03-11 | 1993-08-03 | Hughes Danbury Optical Systems, Inc. | Wavefront sensor having a lenslet array as a null corrector |
| US5241265A (en) | 1992-03-26 | 1993-08-31 | Northern Telecom Limited | Logic function circuit with an array of data stores and their circuit testing |
| US5473392A (en) * | 1992-05-01 | 1995-12-05 | Summit Technology, Inc. | Method and system for topographic measurement |
| US5841511A (en) * | 1992-06-02 | 1998-11-24 | Eyesys Technologies, Inc. | Method of corneal analysis using a checkered placido apparatus |
| DE4222395A1 (en) * | 1992-07-08 | 1994-01-13 | Amtech Ges Fuer Angewandte Mic | Optical system for measuring refraction of eye with light source - has variable imaging optics adjustable in its power of refraction focussing light emanating from light source on retina of eye |
| US5549632A (en) | 1992-10-26 | 1996-08-27 | Novatec Laser Systems, Inc. | Method and apparatus for ophthalmic surgery |
| US5307097A (en) | 1992-11-05 | 1994-04-26 | Kera-Metrics, Inc. | Corneal topography system including single-direction shearing of holograph grating in orthogonal directions |
| JPH06171032A (en) | 1992-12-08 | 1994-06-21 | Teijin Ltd | Laminate for paraglider |
| US5418714A (en) | 1993-04-08 | 1995-05-23 | Eyesys Laboratories, Inc. | Method and apparatus for variable block size interpolative coding of images |
| US5293871A (en) * | 1993-05-05 | 1994-03-15 | Cornell Research Foundation Inc. | System for ultrasonically determining corneal layer thicknesses and shape |
| US5452031A (en) * | 1993-05-05 | 1995-09-19 | Boston Eye Technology, Inc. | Contact lens and a method for manufacturing contact lens |
| JP3305410B2 (en) * | 1993-05-18 | 2002-07-22 | 株式会社トプコン | Ophthalmic equipment |
| US5548354A (en) * | 1993-06-10 | 1996-08-20 | Konan Common Co., Ltd. | Method for observing and photographing a cornea and apparatus for the same |
| AU716040B2 (en) * | 1993-06-24 | 2000-02-17 | Bausch & Lomb Incorporated | Ophthalmic pachymeter and method of making ophthalmic determinations |
| US5474548A (en) * | 1993-07-14 | 1995-12-12 | Knopp; Carl F. | Method of establishing a unique machine independent reference frame for the eye |
| US5502518A (en) * | 1993-09-09 | 1996-03-26 | Scient Optics Inc | Asymmetric aspheric contact lens |
| EP0644411B1 (en) * | 1993-09-17 | 1997-03-26 | ESSILOR INTERNATIONAL (Compagnie Générale d'Optique) | Procedure and apparatus for the absolute measurement of the geometrical or optical structure of an optical component |
| GB9323065D0 (en) | 1993-11-09 | 1994-01-05 | Besca Ltd | A wide field retinal scanning ophthalmoscope |
| US5475452A (en) * | 1994-02-24 | 1995-12-12 | Keravision, Inc. | Device and method for mapping objects |
| US5980513A (en) * | 1994-04-25 | 1999-11-09 | Autonomous Technologies Corp. | Laser beam delivery and eye tracking system |
| US5442412A (en) * | 1994-04-25 | 1995-08-15 | Autonomous Technologies Corp. | Patient responsive eye fixation target method and system |
| US5861955A (en) * | 1994-04-25 | 1999-01-19 | Medjet Inc. | Topographical cornea mapping for corneal vision correction |
| US5632742A (en) * | 1994-04-25 | 1997-05-27 | Autonomous Technologies Corp. | Eye movement sensing method and system |
| US5493391A (en) * | 1994-07-11 | 1996-02-20 | Sandia Corporation | One dimensional wavefront distortion sensor comprising a lens array system |
| US5491524A (en) * | 1994-10-05 | 1996-02-13 | Carl Zeiss, Inc. | Optical coherence tomography corneal mapping apparatus |
| EP0843529B1 (en) * | 1994-10-28 | 2002-06-05 | LaserSight Technologies, Inc. | Multi-camera corneal analysis system |
| US5528791A (en) | 1995-06-23 | 1996-06-25 | New Knight Inc. | Wringer floor mop with pivoting head |
| US5629765A (en) * | 1995-12-15 | 1997-05-13 | Adaptive Optics Associates, Inc. | Wavefront measuring system with integral geometric reference (IGR) |
| US5784146A (en) * | 1995-12-28 | 1998-07-21 | Nidek Co., Ltd | Ophthalmic measurement apparatus |
| US6241355B1 (en) | 1996-03-29 | 2001-06-05 | Brian A. Barsky | Computer aided contact lens design and fabrication using spline surfaces |
| US5785704A (en) * | 1996-07-29 | 1998-07-28 | Mrc Systems Gmbh | Method for performing stereotactic laser surgery |
| US5822035A (en) * | 1996-08-30 | 1998-10-13 | Heidelberg Engineering Optische Messysteme Gmbh | Ellipsometer |
| US5735283A (en) * | 1996-10-09 | 1998-04-07 | Snook; Richard Kieth | Surgical keratometer system for measuring surface topography of a cornea during surgery |
| US6271914B1 (en) | 1996-11-25 | 2001-08-07 | Autonomous Technologies Corporation | Objective measurement and correction of optical systems using wavefront analysis |
| US20010041884A1 (en) | 1996-11-25 | 2001-11-15 | Frey Rudolph W. | Method for determining and correcting vision |
| US5777719A (en) * | 1996-12-23 | 1998-07-07 | University Of Rochester | Method and apparatus for improving vision and the resolution of retinal images |
| US5740803A (en) * | 1997-03-07 | 1998-04-21 | Autonomous Technologies Corporation | Locating the center of the entrance pupil of an eye after pupil dilation |
| US6007204A (en) * | 1998-06-03 | 1999-12-28 | Welch Allyn, Inc. | Compact ocular measuring system |
| US6002484A (en) * | 1999-06-18 | 1999-12-14 | Rozema; Jos J. | Phase contrast aberroscope |
| US6439720B1 (en) * | 2000-01-27 | 2002-08-27 | Aoptics, Inc. | Method and apparatus for measuring optical aberrations of the human eye |
-
1996
- 1996-12-23 US US08/772,977 patent/US5777719A/en not_active Expired - Lifetime
-
1997
- 1997-12-23 CN CNB971815046A patent/CN1184926C/en not_active Expired - Fee Related
- 1997-12-23 WO PCT/US1997/023863 patent/WO1998027863A1/en active IP Right Grant
- 1997-12-23 EP EP97954229A patent/EP0969760B1/en not_active Expired - Lifetime
- 1997-12-23 JP JP52906798A patent/JP4105237B2/en not_active Expired - Lifetime
- 1997-12-23 CA CA002275762A patent/CA2275762C/en not_active Expired - Lifetime
- 1997-12-23 BR BRPI9714178-0A patent/BR9714178B1/en not_active IP Right Cessation
- 1997-12-23 DE DE69739629T patent/DE69739629D1/en not_active Expired - Lifetime
-
1998
- 1998-05-04 US US09/071,794 patent/US5949521A/en not_active Expired - Lifetime
-
1999
- 1999-07-02 US US09/346,309 patent/US6095651A/en not_active Expired - Lifetime
-
2000
- 2000-06-15 HK HK00103587A patent/HK1024157A1/en not_active IP Right Cessation
- 2000-07-28 US US09/628,690 patent/US6379005B1/en not_active Expired - Lifetime
-
2002
- 2002-02-20 US US10/078,163 patent/US6948818B2/en not_active Expired - Lifetime
-
2005
- 2005-08-09 US US11/199,174 patent/US7416305B2/en not_active Expired - Fee Related
-
2008
- 2008-06-24 US US12/145,265 patent/US20080316429A1/en not_active Abandoned
- 2008-06-24 US US12/145,345 patent/US20080259273A1/en not_active Abandoned
- 2008-06-24 US US12/145,264 patent/US20090002628A1/en not_active Abandoned
- 2008-06-24 US US12/145,302 patent/US20080251955A1/en not_active Abandoned
Also Published As
| Publication number | Publication date |
|---|---|
| US20090002628A1 (en) | 2009-01-01 |
| US20080259273A1 (en) | 2008-10-23 |
| US20060044510A1 (en) | 2006-03-02 |
| US20080251955A1 (en) | 2008-10-16 |
| US6948818B2 (en) | 2005-09-27 |
| CN1184926C (en) | 2005-01-19 |
| JP2001507258A (en) | 2001-06-05 |
| AU723645B2 (en) | 2000-08-31 |
| US20030025874A1 (en) | 2003-02-06 |
| US5949521A (en) | 1999-09-07 |
| US5777719A (en) | 1998-07-07 |
| JP4105237B2 (en) | 2008-06-25 |
| US6095651A (en) | 2000-08-01 |
| US20080316429A1 (en) | 2008-12-25 |
| WO1998027863A1 (en) | 1998-07-02 |
| DE69739629D1 (en) | 2009-12-03 |
| AU5806298A (en) | 1998-07-17 |
| CN1245406A (en) | 2000-02-23 |
| EP0969760B1 (en) | 2009-10-21 |
| BR9714178A (en) | 2000-02-29 |
| BR9714178B1 (en) | 2009-01-13 |
| US6379005B1 (en) | 2002-04-30 |
| CA2275762A1 (en) | 1998-07-02 |
| US7416305B2 (en) | 2008-08-26 |
| EP0969760A1 (en) | 2000-01-12 |
| HK1024157A1 (en) | 2000-10-05 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA2275762C (en) | Apparatus for improving vision and resolution of retinal images | |
| US6439720B1 (en) | Method and apparatus for measuring optical aberrations of the human eye | |
| US6578963B2 (en) | Wavefront sensor for objective measurement of an optical system and associated methods | |
| US6905210B2 (en) | Methods and systems for measuring local scattering and aberration properties of optical media | |
| EP1367935B1 (en) | Tomographic wavefront analysis system and method of mapping an optical system | |
| CA2338060C (en) | Apparatus and method for measuring vision defects of a human eye | |
| US6736507B2 (en) | High resolution, multispectral, wide field of view retinal imager | |
| CA2425256A1 (en) | Determination of ocular refraction from wavefront aberration data | |
| MXPA01013364A (en) | Spatial filter for enhancing hartmann shack images and associated methods. | |
| AU723645C (en) | Apparatus for improving vision and resolution of retinal images | |
| Liang et al. | Hartmann-Shack sensor as a component in active optical system to improve the depth resolution of the laser tomographic scanner | |
| Haman | A quick method for analyzing Hartmann-Shack patterns: application to refractive surgery | |
| Bille et al. | The development of wavefront technology and its application to ophthalmology | |
| Goelz et al. | Measurement of the Z-transferfunction in the fovea centralis of the human eye using a new confocal laser scanning device | |
| Artal | Image quality and retinal sampling in the human eye: new experimental and computational results | |
| Larichev et al. | 2 IPLIT RAS Pionerskaya 2, Troick, Moscow region, 142092 Russia Summary. We present the novel instrument combining the Shack-Hartman wave-front sensor, compensator of low order aberrations and bimorph adaptive mirror for high order aberration correction. We have tested the developed instrument in the |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKEX | Expiry |
Effective date: 20171227 |